WO2002083204A1 - Feeding set adaptor - Google Patents

Feeding set adaptor Download PDF

Info

Publication number
WO2002083204A1
WO2002083204A1 PCT/US2001/047884 US0147884W WO02083204A1 WO 2002083204 A1 WO2002083204 A1 WO 2002083204A1 US 0147884 W US0147884 W US 0147884W WO 02083204 A1 WO02083204 A1 WO 02083204A1
Authority
WO
WIPO (PCT)
Prior art keywords
delivery system
pump
tube
solution delivery
sample cell
Prior art date
Application number
PCT/US2001/047884
Other languages
French (fr)
Inventor
Kent F. Beck
James A. Malmstrom
Scott D. Miles
Original Assignee
Zevex, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Zevex, Inc. filed Critical Zevex, Inc.
Priority to EP01991001.7A priority Critical patent/EP1381412B1/en
Priority to DK01991001.7T priority patent/DK1381412T3/en
Priority to JP2002581005A priority patent/JP4255695B2/en
Priority to ES01991001.7T priority patent/ES2496101T3/en
Publication of WO2002083204A1 publication Critical patent/WO2002083204A1/en

Links

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16831Monitoring, detecting, signalling or eliminating infusion flow anomalies
    • A61M5/16854Monitoring, detecting, signalling or eliminating infusion flow anomalies by monitoring line pressure
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/142Pressure infusion, e.g. using pumps
    • A61M5/14212Pumping with an aspiration and an expulsion action
    • A61M5/14232Roller pumps
    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04BPOSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B43/00Machines, pumps, or pumping installations having flexible working members
    • F04B43/0009Special features
    • F04B43/0054Special features particularities of the flexible members
    • F04B43/0072Special features particularities of the flexible members of tubular flexible members
    • FMECHANICAL ENGINEERING; LIGHTING; HEATING; WEAPONS; BLASTING
    • F04POSITIVE - DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS FOR LIQUIDS OR ELASTIC FLUIDS
    • F04BPOSITIVE-DISPLACEMENT MACHINES FOR LIQUIDS; PUMPS
    • F04B43/00Machines, pumps, or pumping installations having flexible working members
    • F04B43/12Machines, pumps, or pumping installations having flexible working members having peristaltic action
    • F04B43/1253Machines, pumps, or pumping installations having flexible working members having peristaltic action by using two or more rollers as squeezing elements, the rollers moving on an arc of a circle during squeezing
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16831Monitoring, detecting, signalling or eliminating infusion flow anomalies
    • A61M2005/16863Occlusion detection
    • A61M2005/16868Downstream occlusion sensors
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/14Infusion devices, e.g. infusing by gravity; Blood infusion; Accessories therefor
    • A61M5/168Means for controlling media flow to the body or for metering media to the body, e.g. drip meters, counters ; Monitoring media flow to the body
    • A61M5/16831Monitoring, detecting, signalling or eliminating infusion flow anomalies
    • A61M2005/16863Occlusion detection
    • A61M2005/16872Upstream occlusion sensors
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/12General characteristics of the apparatus with interchangeable cassettes forming partially or totally the fluid circuit
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/33Controlling, regulating or measuring
    • A61M2205/3306Optical measuring means
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M2205/00General characteristics of the apparatus
    • A61M2205/33Controlling, regulating or measuring
    • A61M2205/3331Pressure; Flow
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M39/00Tubes, tube connectors, tube couplings, valves, access sites or the like, specially adapted for medical use
    • A61M39/22Valves or arrangement of valves
    • A61M39/28Clamping means for squeezing flexible tubes, e.g. roller clamps
    • A61M39/281Automatic tube cut-off devices, e.g. squeezing tube on detection of air
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61MDEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
    • A61M5/00Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
    • A61M5/36Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests with means for eliminating or preventing injection or infusion of air into body
    • A61M5/365Air detectors

Definitions

  • the present invention relates to systems for feeding solutions to patients. More particularly, the present invention relates to a feeding set adaptor which is used in association with a medical solution pump.
  • the pump and an infusion set which is acted on by the pump typically form a system for the monitoring of fluid pressures, for bubble detection and for selective flow occlusion of solutions being fed to a patient.
  • the invention relates to an adaptor which is used to connect various parts of an infusion set and to integrate them with the pump to enable the monitoring of fluid pressures, the detection of bubbles, and the selective occlusion of fluid flow to prevent freeflow conditions.
  • a solution must be fed to a patient over a period of time.
  • the solution is provided directly into the blood stream of the patient.
  • Saline solutions and medications supplied in such a manner are typically referred to as parenteral solutions.
  • an enteral feeding system is used to provide nutrient solutions to patients who, for one reason or another, are unable to eat for themselves.
  • Such a system typically includes a pump which is attached to an input tube connected to a supply container and to an output tube which is connected to a patient. The pump draws nutrient solution from the supply container and delivers the solution to the patient.
  • an enteral feeding pump can adjust its output to deliver a predetermined amount of nutrient solution (or even medication) at a desired rate.
  • nutrient solution or even medication
  • Occlusion can occur, for example, if a fibrous substance is included in the enteral feeding solution and somehow combines to interfere with flow through the tube. Occlusion can also occur if a tube is bent sufficiently to interfere with flow therethrough, or if a roller clamp (as is commonly used for intravenous applications) is not sufficiently opened. Because of the viscosity of the solution, the amount of kinking of the tube or other interference required to interfere with solution flow is significantly less than that required in a parenteral infusion set.
  • enteral feeding systems Yet another concern with enteral feeding systems is that of viscosity of the solution and viscosity changes as a container full of solution is pumped to a patient. Knowing the viscosity of the fluid being pumped through the enteral feeding system is important because different viscosities are pumped at different rates by the enteral feeding pump. For example, a lower quantity of a highly viscous solution will be pumped by a given number of rotations of the enteral feeding pump motor than will be moved by the same pump when the solution has low viscosity. In other words, the amount of solution fed to the patient can differ substantially depending on the solution's viscosity. Thus, unless the pump is able to accurately determine and compensate for viscosity changes in the solution (i.e. by increasing or decreasing the rotations of the pump rotor in a given period of time) , it is difficult to know exactly how much of the solution has been fed to the patient.
  • the fluid flow monitoring mechanism disclosed in U.S. Patent No. 5,720,721 and the anti-freeflow mechanism described in U.S. Patent No. 5,704,584 provided a significant improvement in monitoring for enteral feeding pumps and in control of freeflow situations.
  • the pump taught in U.S. Patent No. 5,720,721 uses two pressure sensors to monitor viscosity and occlusions, and to enable the enteral feeding pump to compensate for the varying amount of solution which will pass through the pump with each rotation of the rotor.
  • the pressure sensors engage the elastic tube of the infusion set and monitor changes in the strain on the infusion set by occlusions and viscosity changes.
  • the strain information can then be processed by the pump and adjustments made to the number of rotations of the pump rotor to compensate. In the event that the occlusion is too severe to compensate by modification of the rotor rotations, the pump is shut down and an alarm signal generated so that replacement tubing may be provided. Also included was an air detector which was disposed in the pump. The air detector was disposed in communication with the pump and used ultrasonic energy to determine if bubbles were present in the conduit . While the pressure sensor system of U.S. Patent No.5, 720, 721 is a significant improvement over the art, it does have limitations. The pressure sensors described in jthe 721 patent are relatively expensive and must be properly mounted in the pump.
  • the person loading the pump must make sure that the upstream and downstream portions of the infusion set are properly loaded in the pump housing so that they engage the pressure sensors in the proper manner. Failure to properly load the infusion set can interfere with the functioning of the pressure sensors. In particular, if the clinician overly stretches the tubing as he or she wraps it around the pump, the tube on one side of the pump rotor will be stretched to a greater degree than the opposing side. This, in turn, can effect pump accuracy if too severe.
  • One manner for decreasing the costs of pressure sensors is to use an optical sensors. While there are several methods for using optical sensors to determine the presence of occlusions, each has significant drawbacks. Some methods only allow the mechanism to determine when the pressure exceeds a certain threshold. This is done by detecting when the expanding tube of the infusion set engages a surface, thereby modifying reflection or refraction of light. Other methods require complex calculations of refraction indexes or otherwise provide relatively limited information on small pressure changes.
  • some methods can vary based on the material from which the infusion set is formed, or based on whether the tube of the infusion set is opaque or transparent .
  • many mechanisms for monitoring pressure within an infusion set lack- an inherent failure detector. For example, if a sensor is configured to sense only when the expanding infusion set tube engages a transparent surface, the failure to record a reflected signal may mean that the tube has not expanded. In certain situations, however, the lack of reflected signal could also mean that the sensor has failed and is either not sending the signal or is not receiving the reflected signal.
  • the pumps also used ultrasonic technology for bubble detection. While this technology is highly accurate, it is also expensive. An ultrasonic sensor can cost as much as 50 times as much as an optical sensor.
  • a feeding set adaptor configured for attachment to an upstream portion, a down stream portion and a pump engaging portion of an infusion set .
  • the feeding set adaptor is attached to a flexible tube which forms the pump engaging portion of the infusion set.
  • the flexible tube is mounted to the adaptor in such a manner that the tube is not disproportionately stretched on either side of the pump mechanism when it is loaded on the pump mechanism.
  • the flexible tube of the infusion set attached to the feeding set adaptor has at least one monitoring portion which is held by the adaptor to prevent stretching of the tube.
  • the monitoring portion is disposed adjacent a sensor which allows the pump to monitor pressure within the tube. Preferably, this is done by an optical sensor which is positioned to monitor the diameter of the tube.
  • the pump can determine the pressure within the tube. If the pressure sensed is above or below predetermined thresholds, the pump can determine that there is an occlusion and will generate an alarm.
  • the flexible tube is secured for monitoring both upstream and downstream from the pump rotor (or other pump mechanism) .
  • the pump can monitor upstream and downstream occlusions.
  • the pressure monitoring can also be used in conjunction with movement of the pump mechanism to more accurately determine solution flow through the pump system.
  • the feeding set adaptor is configured to hold the tube in such a position that the tube neither obstructs all light flow nor allows complete light flow between the two sides of the optical sensor.
  • the signals generated by the optical signal receiver indicate the extent to which the optical signal sent by the optical signal emitter have been obstructed by the tube. If, however, a full reading is received, the pump can indicate that the feeding set adaptor and the associated tube have not been properly mounted in the pump. In contrast, if no reading is received, the pump can generate an alarm indicating that the sensor is malfunctioning, or that the infusion set tube has expanded well beyond the desired threshold.
  • the feeding set adaptor includes a sample cell through which solution being pumped by the pump is passed.
  • the sample cell is configured for monitoring the solution to determine the presence of bubbles.
  • the sample cell has a pair of angled sidewalls.
  • the angled sidewalls are preferably disposed at an angle of 47 to 70 degrees from each other, depending on the indices of refraction of the material used, and are most preferably angled 50 to 60 degrees from one another.
  • the sample cell is configured to fit into a void on a housing disposed adjacent to an optical sensor. Light from the optical sensor passes through the housing and the sample cell in such a manner that it is refracted in one direction if the sample cell is full of liquid and another angle if a bubble is present in the sample cell.
  • the pump is able to monitor for bubbles and to make appropriate corrections in pump flow rate or to generate an alarm if the amount of air present in the solution exceeds desired thresholds .
  • an occluder is disposed within the infusion set.
  • the occluder is configured to prevent free flow of fluids in the infusion set past the occluder.
  • the occluder is also configured, however, to selectively allow solutions to pass by the occluder which are pumped by an enteral feeding pump and the like.
  • the feeding set adaptor includes an occluder which prevents fluid flow through the infusion set when the infusion set has not been disposed in proper engagement with the pump mechanism of the infusion pump, thereby giving control of fluid flow through the infusion set to the pump.
  • the occluder is formed by a stop attached to the feeding set adaptor and placed in the tubing of the infusion set.
  • the stop limits flow through the tube by limiting flow around and/or through the stop when the solution is subject to flow due to gravity.
  • greater pressures are placed on the solution, such as those produced by a pump, the solution is able to flow around and/or through the stop, thereby delivering the solution to the patient.
  • an occluding valve is formed as part of the feeding set adaptor and is disposed in the infusion set.
  • the valve prevents free flow through the infusion set due to gravity, while allowing controlled flow of solution through the infusion set.
  • the occluder is configured to stop fluid flow until the infusion set has been properly loaded into a control mechanism such as a pump. Once properly placed, the interaction between the occluder and the infusion set effectively opens the infusion set to allow solution to flow therethrough.
  • a plurality of the aspects discussed above are integrated into a single feeding set adaptor.
  • FIG. 1A shows a top view of an enteral feeding pump housing formed in accordance with the principles of the prior art
  • FIG. IB shows a top view of a top of an enteral feeding pump housing and a pinch clip occluder formed in accordance with the principles of the prior art
  • FIG. 2A shows a top perspective view of a feeding set adaptor configured in accordance with the principles of the present invention
  • FIG. 2B shows a bottom perspective view of the feeding set adaptor shown in FIG. 2A;
  • FIG. 2C shows a side view of the pump engaging portion of the infusion set
  • FIG. 3 shows a bottom view of an enteral feeding set adaptor having the pump engaging portion of the infusion set disposed therein for mounting on an infusion pump in accordance with the principles of the present invention
  • FIG. 4 shows a fragmented perspective view of an infusion set and a perspective view of a feeding set adaptor and an enteral feeding pump made in accordance with principle of the present invention
  • FIGs . 5 and 5A show close-up, cross-sectional views of the adaptor, flexible tubing and portion of the enteral feeding pump relating to the pressure monitoring mechanism associated with feeding set adaptor;
  • FIGs. 6 and 6A show a close-up, cross-sectional view of the adaptor and the enteral feeding pump portions relating to the detection of air bubbles passing through the infusion set;
  • FIGs. 7 and 7A show close-up, cross-sectional views of the adaptor and infusion set relating to the anti-freeflow mechanism of the present invention
  • FIG. 7B shows a close-up, cross-sectional view of the adaptor, infusion set and enteral feeding pump providing an alternate embodiment of the anti-freeflow mechanism of the present invention.
  • FIG. 7C shows a close-up, cross-sectional view of yet another embodiment of the anti-freeflow mechanism of the present invention.
  • FIG. 1A there is shown a top view of an enteral feeding system taught in U.S. Patent No. 5,720,721.
  • the enteral feeding system generally indicated at 4, has a delivery set 8 including an intake (upstream) tube 10 and an output (downstream) tube 14 connected together by a pair of connectors 18 and a pump tubing segment within an enteral feeding pump 20.
  • the position of the pump tubing segment disposed inside of the pump 20 is represented by the dashed lines 16.
  • the enteral feeding pump 20 includes a housing 24 with a conventional motor unit, generally indicated at 28.
  • the motor unit 28 includes a rotor 30 with a plurality of peristaltic rollers 34 disposed about an exterior of the rotor to move liquid through the enteral feeding pump 20.
  • the rotor 30 is connected by a shaft 32 to a motor (not shown) .
  • the section 38 of the pump tubing segment 16 is disposed about the rotor 30 and rollers 34 and is usually made of a flexible silicone material. Rotating the rotor 30 in the direction indicated by the arrows directionally squeezes the tube section 38 and causes solution to be pushed through the output tube 1 .
  • FIG. 1 Also shown in FIG. 1 is an air detector 40 provided in a proximal position (upstream) from the motor unit 28 along the intake tube 10 to warn medical personnel of an empty supply container or a large bubble in the infusion set.
  • the enteral feeding pump 20 of the present invention includes a pair of pressure sensors 50.
  • two pressure sensors 50a and 50b are disposed along the pump tubing segment 16 adjacent the intake/output tubes to 1) ensure that the tubes are properly mounted in the pump 20; 2) monitor any changes in viscosity which are significant enough to alter the amount of liquid moved by each rotation or partial rotation of the rotor 30; and 3) detect any occlusions in the intake tube 10 or the output tube 14 of the delivery set 8.
  • a retention plate 54 (FIG. 1) is attached to the housing 24 by a screw 58 to hold the pressure sensors 50a and 50b in place.
  • FIGs . 2A and 2B there are shown a top perspective view and a bottom perspective view of a feeding set adaptor, generally indicated at 100, which improves upon the prior art.
  • the feeding set adaptor has a connector portion 104 having a first connector 108 and a second connector 112.
  • the first connector portion 104 also preferably has a small handle 116 which can be used to pull the feeding set adaptor 100 from a pump if necessary.
  • the first connector 108 a functional proximal end 108a which engages the functional distal end of an inflow line (not shown) of an infusion set.
  • the opposing end of the infusion line is typically disposed in communication with a fluid container which holds the solution being delivered to the patient.
  • the first connector 108 will typically be approximately the same diameter as the inflow tube, and the inflow tube is mounted on the first connector by being stretched over the distal end 108a of the connector.
  • the first connector 108 also has a functional distal end 108b.
  • the distal end 180b is preferably configured with an annular barb 108c and a neck portion 108d positioned proximally from the annular barb.
  • the annular barb 108c and neck portion 108d are used to secure a pump engagement portion of the infusion set, which is discussed below regarding FIG. 2C.
  • the distal end 108b of the first connector 108 has conduit 120 which is generally triangular .
  • sample cell 124 Disposed within the first connector 108 is a sample cell 124.
  • the sample cell 124 is used in conjunction with an optical sensor (not shown) to optically determine the presence of air bubbles within the conduit 120.
  • the sample cell 124 is preferably triangular and has sidewall which are offset from one another at an angle of between about 47-70 degrees.
  • the sample cell 124 is made with a wall which forms an equilateral triangle with two sidewalls being disposed at an angle of about 50 to 60 degrees. Such an angle allows light emitted from the optical sensor to be refracted in a first direction if the conduit 120 is filled with liquid, and a second direction if the conduit has any appreciable amount of air.
  • the first tube engagement member 130 preferably includes a wall 132 having generally U-shaped opening 134 which is sized to receive the pump engagement portion of the infusion set.
  • the first tube engagement member 130 also preferably includes a pair of flanges 138 which extend inwardly to partially obstruct the opening and to form a recess which receives a collar (see FIG. 2C) of the pump engagement portion of the infusion set.
  • the pump engagement portion of the infusion set which is generally indicated at 200 in FIG. 2C includes an elongate tube portion 204.
  • the tube portion 204 is preferably a flexible tube made from a medical grade material, such as silicone. Such tubes are commonly used in enteral feeding pumps.
  • the tube portion 204 has a first fitting 208 disposed at a functionally proximal end (i.e. upstream).
  • the first fitting 208 is preferably used by a machine to secure the tube portion 204 and to attach a proximal end 204a of the tube to the distal end 108b of the first connector 108.
  • first abutment member 212 Disposed distally from the first fitting 208 is a first abutment member 212, which is preferably in the form of a collar 216. (In light of the present disclosure, those skilled in the art will appreciate that numerous other abutment configurations could be used to secure the tube portion 204 as described) .
  • the abutment member 212 in particular, and the collar 216 specifically, are designed to nest in the recess 142 against the wall 132 of the first tube engagement member 130. When nested in the recess, the tube portion 204 which is proximal to the collar 216 is held taut between the first tube engagement member 130 and the first connector 108.
  • the pump engaging portion 200 of the infusion set When the pump engaging portion 200 of the infusion set is attached to the distal end 108b of the first connector 108, it is stretched slightly until the collar 216 is slightly passed the flanges 134 of the first tube engagement member 130. The tube portion 204 is then moved between the flanges 134 and the tube released so the contraction of the tube pulls the collar 216 into the recess 142.
  • the second tube engagement member 150 Disposed distally from the first tube engagement member 130 is a second tube engagement member 150.
  • the second tube engagement member preferably includes a wall 152 with a generally U-shaped opening 154. which is sized to receive the pump engagement portion of the infusion set.
  • the second tube engagement member 150 also preferably includes a pair of flanges 158 which extend inwardly to partially obstruct the opening and to form a recess 162 which receives an abutment member 220, which is preferably in the form of a collar 224 (FIG. 2C) .
  • abutment member 220 which is preferably in the form of a collar 224 (FIG. 2C) .
  • the recess 162 preferably faces the recess 142 in the first tube engagement member and works with the collar 224 to prevent the portion of the tube portion 204 disposed proximally adjacent to the collar from being stretched to any significant degree when the central working portion 230 of the pump engaging portion 200 of the infusion set. Likewise, when the pump rotor rotates, the stretching of the tube portion 204 proximally from the collar 224 is minimized.
  • the portion 234 of the tube disposed therebetween is held against movement, this portion forms a relatively isolated monitoring portion 234.
  • Patent Application No. 09/836,852 (Filed concurrently herewith and identified as attorney docket no. 0908.ZEVX.PT, and which is expressly incorporated herein) .
  • the pressure in the infusion set can be determined by having, the tube occlude light in an optical sensor. As the tube expands due to increased pressure or contracts due to a vacuum caused by occlusions, etc., the amount of light which is received by the optical sensor changes, thereby indicating the change in pressure in the tube. Using the diameter of the tube to determine pressure can provide highly accurate readings. However, the accuracy of such readings is diminished if the tube is being stretched inconsistently because having the tube under tension will change the extent to which it expands and contracts due to pressure changes.
  • first and second tube engagement members 130 and 150 and the abutment members 212 and 220 (collars 216 and 224) .
  • These structures interact so that the monitoring portion 234 is held relatively unstretched, regardless of tension from either side. Because most of the tension will occur due to loading the central working portion 230 of the pump engagement portion 200 and rotation of the pump rotator, the second tube engagement member 150 is more critical than the first pump engagement portion.
  • the first pump engagement portion 130 could be omitted while maintaining most of the benefits of the present invention.
  • the feeding set adaptor 100 also includes a third tube engagement member 170.
  • the third tube engagement member preferably includes a wall 132 defining a generally U-shaped opening 174 which is sized to receive the pump engagement portion of the infusion set.
  • the third tube engagement member 170 also preferably includes a pair of flanges 178 which extend inwardly to partially obstruct the opening and to form a recess 182 which receives an abutment member 240, which is preferably in the form of a collar 244 (FIG. 2C) .
  • the recess 182 preferably faces in the same direction as the recess 162 in the second tube engagement member 150.
  • the collars 224 and 244 are disposed in recesses 162 and 182. This substantially isolates the central working portion 230 and prevents rotation of the pump rotor from causing tension either upstream or downstream from the collars 224 and 244, respectively.
  • the feeding set adaptor 100 further comprises a fourth tube engagement member 186.
  • the fourth tube engagement member 186 preferably includes a wall having a generally U-shaped opening 188.
  • a pair of flanges 190 are disposed adjacent the U-shaped opening to partially obstruct the opening and to form a recess 192.
  • the pump engaging portion 200 of the infusion set includes an abutment member 250 in the form of a collar 254 which is configured to nest in the recess 192.
  • the recess 192 of the fourth tube engagement member 186 faces the same direction as first tube engagement member 130 and the third and fourth tube engagement members act together in the same manner as the first and second engagement members to isolate a second monitoring portion 260 on the tube 204.
  • the infusion pump is able to optically monitor both the upstream pressure between the first and second engagement members 130 and 150, and the downstream pressure between the third and fourth engagement members.
  • the pump can readily determine if an occlusion in the infusion set is inhibiting delivery of solution to the patient.
  • the feeding set adaptor 100 also includes an anti- freeflow mechanism 300.
  • the anti-freeflow mechanism 300 is in the form a small ball 304 which is attached to the proximal (i.e. upstream) end 112a of the second connector 112 by a small wall 308.
  • the wall 308 is configured to provide minimal resistance to flow of liquid into the proximal end 112a of the second connector 112.
  • the anti-freeflow mechanism 300 is inserted into the distal end 204b of the tube portion 204.
  • the tube portion 204 is then advanced until the distal end 204b passes over an annular barb 112c and rests on the neck 112d of the second connector 112.
  • a second fitting 268 on the tube portion 204 is typically used so that a machine can readily mount the distal end
  • the small ball 304 will prevent solution flow through the tube portion 204 unless the solution is under sufficient pressure.
  • the small ball 308 will prevent flow through the tube portion 204 if the solution is simply subject to gravity. However, if the solution is placed under sufficient pressure, the flexible material (typically silicone) of the tube portion 204 will expand and allow solution to flow past the small ball 308. This is accomplished as the pump drives solution through the infusion set. If the pump is not properly engaging the central working portion 230 of the tube portion 204, there will not be enough pressure to bypass the anti-freeflow mechanism 300. In other words, unless the pump is in control of the fluid flow, no fluid will flow through the infusion set and a freeflow situation will not develop.
  • the flexible material typically silicone
  • the solution in the tube portion 204 has been driven past the anti-freeflow mechanism 300, the solution passes into the proximal end 112a of the second connector 112.
  • the distal end (downstream) 112b of the second connector 112 is disposed in engagement with a patient portion of the infusion set (not shown) .
  • the patient portion of the infusion set is slid over the second connector 112 and retained in a frictional engagement. It can, however, be attached by other means .
  • FIG. 3 there is shown a bottom view of an enteral feeding set adaptor 100 having the pump engaging portion 200 of the infusion set disposed therein for mounting on an infusion pump in accordance with the principles of the present invention.
  • the central working portion 230 of the pump engaging portion 200 extends outwardly from the feeding set adaptor 100 in a loop.
  • the portion of the infusion set which engages the pump rotor can be stretched unevenly as it is mounted on the pump. This can interfere with monitoring of pressure within the infusion set. Additionally, stretching the tube and wrapping it around the pump rotor can take some coordination.
  • the feeding set adaptor 100 and pump engaging portion 200 of the infusion set is loaded by simply engaging the far side of the loop 230a against the pump rotor and pulling the feeding set adaptor 100 until it can be inserted in the pump.
  • the risk of the central working portion 230 being stretched unevenly is virtually eliminated. Additionally, it takes very little coordination to properly load the feeding set adaptor 100 in the pump.
  • the user simply loops the end 230a of the looped central working portion 230 over the rotor and pulls back on the feeding set adaptor 100 until it is in alignment with a cavity on the pump, and releases the feeding set adaptor.
  • FIG. 4 there is shown a fragmented perspective view of an infusion set, generally indicated at 310 and a perspective view of a feeding set adaptor 100 and an enteral feeding pump, generally indicated at 320, made in accordance with principle of the present invention.
  • the infusion set 310 includes an inflow tube 314 which is typically connected to a solution container (not shown) , such as a plastic bag holding enteral feeding solution, and an outflow tube 318, which is generally connected to an adaptor (not shown) which engages a balloon catheter which traverses the abdominal wall of the patient.
  • the inflow tube 314 is connected to the pump engaging portion 200 of the infusion set 310 by the first connector 108. As discussed above, the solution passing through the inflow tube 314 and the first connector 108 passes through the sample cell 124. Due to the configuration of the feeding set adaptor 100, the sample cell 124 nests in a channel 324 of the infusion pump 320. A portion of the channel 324 defines a housing 328 which is preferably made of a generally translucent plastic. The housing 328 serves the dual purpose of protecting an optical sensor (not visible in FIG. 4) from liquids, and of refracting light which is emitted and received by various parts of the optical sensor. As the solution passes through the sample cell 124, the optical sensor sends light through the housing 328 and sample cell 124.
  • the sample cell 124 is specifically designed so that it always sends some light to the optical detector to provide an integrity check of the optical sensor. If a bubble is present, however, a light emitted by the optical sensor is refracted to the optical detector. The amount of light which is refracted gives a reliable indication of whether a bubble is present, and the size of the bubble. If the bubble exceeds desired thresholds, the pump 320 can generate an alarm. The alarm may be audible, or simply appear on a display screen 332 on the pump 320.
  • the monitoring portion 234 is disposed between the first and second tube engagement members 130 and 150, and is disposed in a distal section 324a of the channel 324.
  • an optical sensor Disposed in the walls of the distal section 324a of the channel 324 is an optical sensor (not shown) .
  • the optical sensor sends light between an optical signal emitter and an optical signal detector.
  • the diameter of the monitoring portion 234 changes as pressure changes within the tube.
  • the change in diameter of the monitoring portion 234 changes the amount of light which is detected by the optical detector and allows the pump 320 to determine pressure within the monitoring portion without direct contact.
  • the inflow line 314 of the infusion set 310 were to be kinked or otherwise occluded, flow through the inflow line would be reduced.
  • the pump rotor 340 of the infusion pump 320 rotates, it will develop a vacuum upstream from the rotor. Because the inflow line 314 is occluded, the vacuum created by the rotation of the rotor 340 will be greater in magnitude and will remain longer than if flow through the inflow tube were not obstructed.
  • the vacuum will cause the monitoring portion 234 of the pump engaging portion 200 to collapse to a greater degree and remain in a collapsed state for a longer period of time.
  • the optical sensor detects the collapse because more light will be detected by the optical detector and for a longer period of time.
  • the pump 320 monitors the readings of the optical sensor. If the readings of the optical detector fall outside of a predetermined range, the pump 320 will generate an alarm indicating the presence of an occlusion. It may also automatically stop the pump 320 until the occlusion situation has been resolved.
  • the solution passes out of the monitoring portion 234, it passes into the central working portion 230 of the pump engaging portion 200 of the infusion set 310.
  • the central working portion 230 is engaged by a plurality of rollers 344 on the pump rotor 340.
  • the rollers 344 pinch off sections of the tube and advance theoretically known volumes of solution with each rotation. (The actual volumes moved are partially dependent on the pressures on the solution both upstream and downstream from the rotor 340) .
  • the pump 320 can deliver a known volume of solution to the patient .
  • the second monitoring portion 260 which is disposed between the third and fourth tube engagement portions 170 and 186.
  • the second monitoring portion 260 rests in a channel 354 in the pump 320 which is preferably disposed parallel to channel 324.
  • the channel 354 also has an optical sensor which functions in substantially the same manner as the sensor discussed in association with the monitoring portion 234. The only signficiant difference between the two is that which the monitoring portion 234 will generally collapse due to vacuum created by the pump rotor 340 and upstream occlusions, the second monitoring portion 260 will generally expand due to solution being forced down stream by the pump rotor 340 and any occlusions downstream which inhibit the downstream flow of solution.
  • the solution Once the solution passes out of the second monitoring portion 260, it must flow around the anti- freeflow device 300. As mentioned above, gravity alone is insufficient to develop flow around the anti- freeflow device 300. However, the rotation of the pump rotor 340 pushes solution downstream with sufficient force that the tube 204 adjacent the anti- freeflow device will expand and create a channel around the ball 304, thereby allowing the solution to flow down stream to the patient.
  • the solution flows through the second connector 112 and into the outflow portion 318 of the infusion set 310 which delivers the solution to the patient.
  • FIGs. 5 and 5A there are shown close-up, cross-sectional views of the feeding set adaptor 100, flexible tubing 204 of the pump engaging portion 200 and a portion of the enteral feeding pump 320 relating to the pressure monitoring mechanism associated with feeding set adaptor.
  • the enteral feeding pump 320 has two channels 324 and 354 which receive the feeding set adaptor 100.
  • the monitoring portion 230 of the flexible tubing 204 of the pump engaging portion 200 is disposed in the first chan Disposed on opposing sides of the first channel 324 is an optical sensor 400.
  • the optical sensor includes a optical signal emitter 404 and an optical signal detector 408. Each is provided with leads 412 for communication with the enteral feeding pump.
  • the optical signal emitter 404 In response to an electrical signal from the pump 324, the optical signal emitter 404 emits light energy, indicated by dashed line 420.
  • light energy indicated by dashed line 420.
  • Those skilled in the art will appreciate that various wavelengths of light may be used. Currently, it is anticipated that infrared light will be preferred.
  • the flexible tube 204 forming monitoring portion 230 is positioned to obstruct some of the light.
  • the extent to which the light is obstructed depends on the diameter of the flexible tube 204 in the monitoring portion 230. This diameter, depends on the pressure within the tube.
  • the voltage or other readings of the sensor correlates with the pressure inside of the tube.
  • the flexible tube 204 forming the monitoring portion 230 is disposed so that it always obstructs some light, but does not obstruct all light flow between the optical signal emitter and the optical signal detector. This can be used to verify the integrity of the sensor and proper loading of the tubing. If the optical signal detector 408 gives the maximum voltage reading, the tubing 204 is not loaded properly. If, in contrast, no optical signal is received by the optical signal detector 408, the sensor 400 is defective and must be serviced or replaced.
  • FIG. 5A there is shown a view similar to that of FIG. 5.
  • the diameter of the tube 204 has decreased. This typically occurs with each rotation of the pump rotor (FIG. 4) as a temporary vacuum is created as solution is forced through the infusion set.
  • the extent of the vacuum and its duration is related to the presence of occlusions, and/or the viscosity of the solution.
  • the sensor 400 detects the extent of the reduced diameter of the tube 204 in the monitoring portion 230 by the amount of light received by the optical signal detector 408. The optical sensor 400 is thereby able to determine the negative pressure within the tube.
  • the pump 320 is then able to make adjustments to rotor rotations to ensure accurate volume delivery. It can also detect an occlusion that should be resolved and generate an alarm.
  • the pump 320 also has a second optical sensor 400' which is disposed along the second monitoring portion 260 which is down stream from the pump rotor (FIG. 4) .
  • the sensor 400' has an optical signal emitter 404 and an optical signal detector 408 which have leads 412 for communicating with the pump.
  • the sensor 400' operates in substantially the same manner as the optical sensor 400 and is therefor not discussed in detail .
  • the sensor 400' will detect pressure increase in the second monitoring portion 260 with each rotor rotation, instead of the pressure decreases associated with the first monitoring portion 230.
  • the rotor FIG. 4
  • the pressure in the second monitoring portion 260 will increase.
  • the increase in pressure causes the diameter of the second monitoring portion to increase and decreasing the amount of light received by the optical signal detector 408.
  • the sensor 400' and monitoring portion 260 can be configured in a variety of ways to achieve the goals of the present invention.
  • the tube 204 is positioned within the sensor such that it will always occlude some light, but will never fully occlude all light from the optical signal emitter 404 to the optical signal emitter 408.
  • a full voltage reading indicates that the tube 204 forming the monitoring portion 260 is not properly loaded.
  • a zero reading indicates that the sensor 400' has malfunctioned and must be serviced or replaced.
  • the tube 204 and sensor 400' could be disposed in communication such that the threshold pressure occludes all light and therefore generates an alarm. While such a configuration meets the requirements of generating an alarm and/or shutting off the pump 320 when the pressure is too high, it has the disadvantage of not distinguishing between a faulty sensor in the pump and an unacceptably high pressure in the infusion set .
  • FIGs. 6 and 6A show a close-up, cross-sectional view of the adaptor and the enteral feeding pump portions relating to the detection of air bubbles passing through the infusion set.
  • the sample cell 124 is disposed in the channel 324 of the pump.
  • the channel 324 has a portion 324b which is defined by a sloped housing 430.
  • the sloped housing 430 is preferably formed of a clear plastic, such as ABS and has walls 430a and 430b which are offset from one another at an angle of between about 45-100 degrees (most preferably about 60 degrees) , and preferably between 40 and 67.5 degrees from horizontal, and a base 432.
  • the housing also preferably has a flanged portion 434.
  • the housing 430 helps both with bubble detection as explained below, and prevents water or other hazzards from entering the pump 320.
  • the optical sensor 440 Disposed adjacent the housing 430 is an optical sensor 440.
  • the optical sensor 440 has an optical signal emitter 444 and an optical signal detector 448 which are disposed on opposing sides of the housing 430.
  • Leads 452 are provided for the optical sensor 440 and pump 320 to send electronic signals to one another.
  • the sample cell 124 is placed in the channel 324 so that it is spaced away from the housing 430 slightly and forms an air chamber 458 between the sample cell and housing. While it is preferred that the conduit 460 formed by the sample cell 124 has a cross-section which forms an inverted equilateral triangle and the sample cell 124 preferably has two walls disposed at 60 degrees from one another, the walls defining the conduit need not form a triangle. As shown in FIG. 6, the walls have a base 464 which is formed at the bottom of the inverted triangle. Additionally, the top wall 468 could be curved or vaulted to provide the conduit with a diamond shape. Also, as set forth in more detail in U.S. Patent Application Serial No. 09/836, 840 (identified as
  • the difference indices of refraction of the plastic sample chamber 124 and the air in the conduit 460 causes the air to be refracted to a much greater degree as shown by the upper dashed line in FIG. 6A.
  • the light is then refracted again as it passes from the air in the conduit to the opposing sidewall 430b, through the air chamber 458 and through the housing 430.
  • the refraction is such that the light is directed to the optical signal detector 448. If an air bubble is present in the conduit 460, it will direct an increased amount of light to the optical signal detector 448.
  • the amount of light refracted to the optical signal detector 408 is proportional to the size of the air bubble.
  • the voltage reading obtained from the optical signal detector 448 is proportional to the size of the bubble.
  • the base 464 of the sample cell 124 assists in the important role of integrity checking the optical sensor 440.
  • the base 464 is positioned so that it will always allow some light through to impact the optical signal detector 448 as shown by the lower dashed line in FIG. 6A. Thus, if the optical signal detector 448 indicates a reading of zero, an alarm can be generated indicating that the sensor 440 has failed. Likewise, the refraction of light is controlled so that too high of a reading indicates that the sample cell 124 has not been properly loaded in the channel 324.
  • FIGs. 7 and 7A there are shown close-up, cross-sectional views of the feeding set adaptor 100 and the pump engaging portion 200 of the infusion set 310 as they relate to the anti-freeflow mechanism 300 of the present invention. It is important to prevent an infusion set from providing uncontrolled solution to the patient. While many enteral feeding systems have roller clamps or other pinch clip occluders, most devices do not affirmatively prevent fluid flow when the pump is not controlling the flow. In contrast, the anti-freeflow mechanism 300 only allows fluid flow when the pump is actively driving solution through the system.
  • the anti-freeflow mechanism shown in FIGs. 7 and 7A is a small substantially ball-shaped member 304 which is sized slightly larger than the inside diameter of the flexible tube 204 which forms the pump engaging portion 200 of the infusion set 310. As such, the ball-shaped member 304 prevents fluid flow under gravity pressures. If, however, a pressure well above that caused by gravity is developed in the flexible tube 204, the flexible tube will expand and develop a channel 480 about the exterior of the ball- shaped member 304. (It will be appreciated that other shapes may also be used) .
  • the channel 480 is opened each time the pump rotor drives solution through the pump engaging portion 200 of the infusion set 310 and allows solution to flow downstream.
  • the configuration is advantageous because it will not allow a freeflow condition to develop, even if the feeding set adaptor 100 is properly mounted in the pump 320 and the pump engaging portion 200 of the infusion set 310 has simply been pulled out of engagement with the pump rotor.
  • FIG. 7B there is shown a cross- sectional view of the adaptor 100, pump engaging portion 200 of the infusion set 310 and enteral feeding pump 320 providing an alternate embodiment of the anti-freeflow mechanism of the present invention.
  • the channel can be opened by interaction of a pump cover 500, the anti-freeflow mechanism 300 and the channel 354 of the pump 320.
  • the cover 500 preferably has an engagement member 504 which is configured to forcefully engage the flexible tube on the opposite side of the tube from the anti- freeflow mechanism.
  • the channel 354 also may have a stop 510 which engages the outside of the flexible tube 204 opposite the anti-freeflow mechanism 300.
  • FIG. 7C there is shown a close-up, cross-sectional view of yet another embodiment of the anti-freeflow mechanism 300' of the present invention. Instead of using a ball-shaped member 304 inside of the tube, the embodiment shown in FIG.
  • FIG. 7C shows a flap 304' which is disposed in the connector 112.
  • the flap is configured to substantially prevent fluid flow through the connector if pressures are equal to or less than typically encountered due to gravity. If a desired pressure threshold is passed, the flap 304' is forced open and allows solution to flow down stream.
  • the flap 304' could be configured to remain open once deflected by the solution pressure, or could be mounted such that the flap 304' returns to its original position once the solution pressures are insufficient to hold the flap open.
  • the adaptor enables the integration of the various functions discussed above, and provides improved pressure monitoring, anti-freeflow and bubble detection at a price well below the systems of the prior art. Additionally, the feeding set adaptor increases the ease of loading and unloading the tube engaging portion of the infusion set. While numerous different embodiments of the present invention have been disclosed, those skilled in the art will appreciate numerous modifications which can be made without departing from the scope and spirit of the present invention. The appended claims are intended to cover such modifications.

Abstract

A feeding set adaptor (100) and related system for delivering solutions utilize a feeding set adaptor which engages a pump engaging portion (200) of an infusion set and the feeding set adaptor structure to provide monitoring portions for detecting pressures within the infusion set, a sample cell (124) for determining the presence of air within an infusion set, and an anti-fleeflow device (300) for selectively preventing freeflow through the infusion set. The feeding set adaptor is configured for mounting on an infusion pump (320) which moves solution through the infusion set for delivery to a patient.

Description

FEEDING SET ADAPTOR
BACKGROUND OF THE INVENTION
1. Field of the Invention.
The present invention relates to systems for feeding solutions to patients. More particularly, the present invention relates to a feeding set adaptor which is used in association with a medical solution pump. The pump and an infusion set which is acted on by the pump typically form a system for the monitoring of fluid pressures, for bubble detection and for selective flow occlusion of solutions being fed to a patient. Specifically, the invention relates to an adaptor which is used to connect various parts of an infusion set and to integrate them with the pump to enable the monitoring of fluid pressures, the detection of bubbles, and the selective occlusion of fluid flow to prevent freeflow conditions.
2. State of the Art.
There are numerous situations in which a solution must be fed to a patient over a period of time. In some situations, the solution is provided directly into the blood stream of the patient. Saline solutions and medications supplied in such a manner are typically referred to as parenteral solutions. In contrast to a parenteral system, an enteral feeding system is used to provide nutrient solutions to patients who, for one reason or another, are unable to eat for themselves. Such a system typically includes a pump which is attached to an input tube connected to a supply container and to an output tube which is connected to a patient. The pump draws nutrient solution from the supply container and delivers the solution to the patient. By adjusting the number of rotations of the motor, or the frequency of rotations, in the pump, an enteral feeding pump can adjust its output to deliver a predetermined amount of nutrient solution (or even medication) at a desired rate. A significant problem with many currently available enteral feeding systems, is that the intake and output tubes may become occluded. Unlike parenteral solutions, enteral feeding solutions have a relatively high viscosity, as they must carry sufficient nutrition to sustain the patient.
Occlusion can occur, for example, if a fibrous substance is included in the enteral feeding solution and somehow combines to interfere with flow through the tube. Occlusion can also occur if a tube is bent sufficiently to interfere with flow therethrough, or if a roller clamp (as is commonly used for intravenous applications) is not sufficiently opened. Because of the viscosity of the solution, the amount of kinking of the tube or other interference required to interfere with solution flow is significantly less than that required in a parenteral infusion set.
If the intake tube becomes occluded, insufficient solution may be supplied to the pump, and thus to the patient. If the output tube becomes occluded, the flow of solution may be blocked, or the solution may be delivered suddenly at unusually high pressures. Additionally, medical personnel may fail to notice that the supply container is out of solution, or may not properly mount the intake and/or output tubes in the pump, thereby preventing the proper amount of solution from being delivered to the patient. Any of these scenarios can have tragic consequences if allowed to continue for a prolonged period of time.
Yet another concern with enteral feeding systems is that of viscosity of the solution and viscosity changes as a container full of solution is pumped to a patient. Knowing the viscosity of the fluid being pumped through the enteral feeding system is important because different viscosities are pumped at different rates by the enteral feeding pump. For example, a lower quantity of a highly viscous solution will be pumped by a given number of rotations of the enteral feeding pump motor than will be moved by the same pump when the solution has low viscosity. In other words, the amount of solution fed to the patient can differ substantially depending on the solution's viscosity. Thus, unless the pump is able to accurately determine and compensate for viscosity changes in the solution (i.e. by increasing or decreasing the rotations of the pump rotor in a given period of time) , it is difficult to know exactly how much of the solution has been fed to the patient.
Yet another problem which is of concern during the administration of enteral feeding solutions is the presence of air bubbles. While very small air bubbles will not cause harm, large bubbles entering the blood stream can cause serious medical complications and even death. Thus, it is important to monitor the solution to ensure that any bubbles present do not exceed the desired threshold.
Still another problem which is present in enteral feeding systems, and the like, is freeflow. Often, the infusion set is placed in a free standing arrangement in which gravity forces the solution into the patient . The rate at which the solution enters the patient can be roughly controlled by various clamps, such as roller clamps, which are currently available on the market. In many applications, it is necessary to precisely control the amount of solution which enters the patient. When this is the case, a regulating device, such as an enteral feeding pump, is placed along the infusion set to control the rate at which the solution is fed to the patient. In applications where a pump, etc., is used, the clamps used to regulate flow are typically opened to their fullest extent to prevent the clamp from interfering with the proper functioning of the pump. The clamp is opened with the expectation that the enteral feeding pump will control fluid flow through the infusion set .
It is not uncommon, for emergencies or other distractions to prevent the medical personnel from properly loading the infusion set in the enteral feeding pump. When the infusion set is not properly loaded in the pump and the clamp has been opened, a situation known as freeflow often develops. The force of gravity causes the solution to flow freely into the patient unchecked by the pump or other regulating device. Under a freeflow condition, an amount of solution many times the desired dose can be supplied to the patient within a relatively short time period. This can be particularly dangerous if the solution contains potent medicines and/or the patient's body is not physically strong enough to adjust to the large inflow of solution.
Numerous devices have been developed in an attempt to prevent free flow conditions. Such devices, however, typically add significantly to the overall cost of the infusion set and some provide only marginal protection against free flow. Thus, there is a need for a device that prevents a freeflow condition while allowing controlled flow through the infusion set. There is also a need for such a device which prevents freeflow if an infusion set is not properly mounted in a pump or other regulating means . Furthermore, there is a need for a device which prevents freeflow and which is inexpensive and easy to use.
The fluid flow monitoring mechanism disclosed in U.S. Patent No. 5,720,721 and the anti-freeflow mechanism described in U.S. Patent No. 5,704,584 (both of which are expressly incorporated herein) provided a significant improvement in monitoring for enteral feeding pumps and in control of freeflow situations. As shown in FIG. 1A, the pump taught in U.S. Patent No. 5,720,721 uses two pressure sensors to monitor viscosity and occlusions, and to enable the enteral feeding pump to compensate for the varying amount of solution which will pass through the pump with each rotation of the rotor. The pressure sensors engage the elastic tube of the infusion set and monitor changes in the strain on the infusion set by occlusions and viscosity changes. The strain information can then be processed by the pump and adjustments made to the number of rotations of the pump rotor to compensate. In the event that the occlusion is too severe to compensate by modification of the rotor rotations, the pump is shut down and an alarm signal generated so that replacement tubing may be provided. Also included was an air detector which was disposed in the pump. The air detector was disposed in communication with the pump and used ultrasonic energy to determine if bubbles were present in the conduit . While the pressure sensor system of U.S. Patent No.5, 720, 721 is a significant improvement over the art, it does have limitations. The pressure sensors described in jthe 721 patent are relatively expensive and must be properly mounted in the pump. Additionally, the person loading the pump must make sure that the upstream and downstream portions of the infusion set are properly loaded in the pump housing so that they engage the pressure sensors in the proper manner. Failure to properly load the infusion set can interfere with the functioning of the pressure sensors. In particular, if the clinician overly stretches the tubing as he or she wraps it around the pump, the tube on one side of the pump rotor will be stretched to a greater degree than the opposing side. This, in turn, can effect pump accuracy if too severe. One manner for decreasing the costs of pressure sensors is to use an optical sensors. While there are several methods for using optical sensors to determine the presence of occlusions, each has significant drawbacks. Some methods only allow the mechanism to determine when the pressure exceeds a certain threshold. This is done by detecting when the expanding tube of the infusion set engages a surface, thereby modifying reflection or refraction of light. Other methods require complex calculations of refraction indexes or otherwise provide relatively limited information on small pressure changes.
Additionally, some methods can vary based on the material from which the infusion set is formed, or based on whether the tube of the infusion set is opaque or transparent . In addition to the above, many mechanisms for monitoring pressure within an infusion set lack- an inherent failure detector. For example, if a sensor is configured to sense only when the expanding infusion set tube engages a transparent surface, the failure to record a reflected signal may mean that the tube has not expanded. In certain situations, however, the lack of reflected signal could also mean that the sensor has failed and is either not sending the signal or is not receiving the reflected signal.
In addition to the concerns with pressure sensing technology of the prior pumps, the pumps also used ultrasonic technology for bubble detection. While this technology is highly accurate, it is also expensive. An ultrasonic sensor can cost as much as 50 times as much as an optical sensor.
In addition to the above, the anti-freeflow technology discussed in U.S. Patent 5,704,584 has limitations. While the occluder mechanism works well, it is relatively expensive to form a separate mechanism to selectively stop flow through the infusion set. A separate pinch clip occludes such as that shown in FIG. IB can add fifteen to twenty percent to the cost of an infusion set. While the cost per unit is rather small, daily replacement of the infusion set can add up to significant costs. In a highly competitive medical environment, even a few cents per unit can dramatically effect sales quantities .
Thus, there is a need for a mechanism which can enable improved pressure monitoring, improved air detection and improved flow occlusion. Such a mechanism should be relatively inexpensive and should lessen the likelihood of errors in use of the pump and infusion set. Furthermore, it should enable the use of infusion sets made from a variety of materials.
SUMMARY OF THE INVENTION
Thus, it is an object of the present invention to provide a mechanism which allows improved method monitoring viscosity and/or occlusions in an infusion set. It is another object of the present invention to provide such a mechanism which facilitates the monitoring of viscosity and occlusions with an optical sensor system.
It is another object of the present invention to provide a mechanism which facilitates the optical monitoring of solution to determine the presence of bubbles in the solution.
It is another object of the present invention to provide a mechanism which prevents free flow through an infusion set unless fluid flow through the infusion set is being driven by the pump.
It is yet another object of the present invention to provide an integrated adaptor which is disposed along an infusion set which facilitates pressure monitoring, bubble monitoring and an anti-free flow device.
The above and other objects of the present invention are realized in specific illustrated embodiments of a feeding set adaptor configured for attachment to an upstream portion, a down stream portion and a pump engaging portion of an infusion set .
In accordance with one aspect of the invention, the feeding set adaptor is attached to a flexible tube which forms the pump engaging portion of the infusion set. The flexible tube is mounted to the adaptor in such a manner that the tube is not disproportionately stretched on either side of the pump mechanism when it is loaded on the pump mechanism.
In accordance with another aspect of the invention, the flexible tube of the infusion set attached to the feeding set adaptor has at least one monitoring portion which is held by the adaptor to prevent stretching of the tube. The monitoring portion is disposed adjacent a sensor which allows the pump to monitor pressure within the tube. Preferably, this is done by an optical sensor which is positioned to monitor the diameter of the tube. By sensing changes in the diameter of the tube, the pump can determine the pressure within the tube. If the pressure sensed is above or below predetermined thresholds, the pump can determine that there is an occlusion and will generate an alarm.
In a preferred embodiment, the flexible tube is secured for monitoring both upstream and downstream from the pump rotor (or other pump mechanism) . Thus, the pump can monitor upstream and downstream occlusions. The pressure monitoring can also be used in conjunction with movement of the pump mechanism to more accurately determine solution flow through the pump system.
In a preferred embodiment, the feeding set adaptor is configured to hold the tube in such a position that the tube neither obstructs all light flow nor allows complete light flow between the two sides of the optical sensor. Between the two extremes of receiving a full optical signal and no optical signal, the signals generated by the optical signal receiver indicate the extent to which the optical signal sent by the optical signal emitter have been obstructed by the tube. If, however, a full reading is received, the pump can indicate that the feeding set adaptor and the associated tube have not been properly mounted in the pump. In contrast, if no reading is received, the pump can generate an alarm indicating that the sensor is malfunctioning, or that the infusion set tube has expanded well beyond the desired threshold. In accordance with another aspect of the invention, the feeding set adaptor includes a sample cell through which solution being pumped by the pump is passed. The sample cell is configured for monitoring the solution to determine the presence of bubbles. Preferably, the sample cell has a pair of angled sidewalls. The angled sidewalls are preferably disposed at an angle of 47 to 70 degrees from each other, depending on the indices of refraction of the material used, and are most preferably angled 50 to 60 degrees from one another.
The sample cell is configured to fit into a void on a housing disposed adjacent to an optical sensor. Light from the optical sensor passes through the housing and the sample cell in such a manner that it is refracted in one direction if the sample cell is full of liquid and another angle if a bubble is present in the sample cell. Thus, the pump is able to monitor for bubbles and to make appropriate corrections in pump flow rate or to generate an alarm if the amount of air present in the solution exceeds desired thresholds . In accordance with one aspect of the invention, an occluder is disposed within the infusion set. The occluder is configured to prevent free flow of fluids in the infusion set past the occluder. The occluder is also configured, however, to selectively allow solutions to pass by the occluder which are pumped by an enteral feeding pump and the like.
In accordance with another aspect of the invention, the feeding set adaptor includes an occluder which prevents fluid flow through the infusion set when the infusion set has not been disposed in proper engagement with the pump mechanism of the infusion pump, thereby giving control of fluid flow through the infusion set to the pump.
In one embodiment of the invention, the occluder is formed by a stop attached to the feeding set adaptor and placed in the tubing of the infusion set. The stop limits flow through the tube by limiting flow around and/or through the stop when the solution is subject to flow due to gravity. However, when greater pressures are placed on the solution, such as those produced by a pump, the solution is able to flow around and/or through the stop, thereby delivering the solution to the patient.
In accordance with another embodiment of the present invention, an occluding valve is formed as part of the feeding set adaptor and is disposed in the infusion set. The valve prevents free flow through the infusion set due to gravity, while allowing controlled flow of solution through the infusion set.
In accordance with another aspect of the invention, the occluder is configured to stop fluid flow until the infusion set has been properly loaded into a control mechanism such as a pump. Once properly placed, the interaction between the occluder and the infusion set effectively opens the infusion set to allow solution to flow therethrough.
In accordance with still yet another aspect of the invention, a plurality of the aspects discussed above are integrated into a single feeding set adaptor. By integrating the various aspect discussed above, the health care professional or patient who loads the pump with the infusion set can be assured that the safety and monitoring aspects discussed above are being accomplished without the need to check multiple systems . BRIEF DESCRIPTION OF THE DRAWINGS
The above and other objects, features and advantages of the invention will become apparent from a consideration of the following detailed description presented in connection with the accompanying drawings in which:
FIG. 1A shows a top view of an enteral feeding pump housing formed in accordance with the principles of the prior art;
FIG. IB shows a top view of a top of an enteral feeding pump housing and a pinch clip occluder formed in accordance with the principles of the prior art; FIG. 2A shows a top perspective view of a feeding set adaptor configured in accordance with the principles of the present invention;
FIG. 2B shows a bottom perspective view of the feeding set adaptor shown in FIG. 2A;
FIG. 2C shows a side view of the pump engaging portion of the infusion set;
FIG. 3 shows a bottom view of an enteral feeding set adaptor having the pump engaging portion of the infusion set disposed therein for mounting on an infusion pump in accordance with the principles of the present invention;
FIG. 4 shows a fragmented perspective view of an infusion set and a perspective view of a feeding set adaptor and an enteral feeding pump made in accordance with principle of the present invention;
FIGs . 5 and 5A show close-up, cross-sectional views of the adaptor, flexible tubing and portion of the enteral feeding pump relating to the pressure monitoring mechanism associated with feeding set adaptor;
FIGs. 6 and 6A show a close-up, cross-sectional view of the adaptor and the enteral feeding pump portions relating to the detection of air bubbles passing through the infusion set;
FIGs. 7 and 7A show close-up, cross-sectional views of the adaptor and infusion set relating to the anti-freeflow mechanism of the present invention;
FIG. 7B shows a close-up, cross-sectional view of the adaptor, infusion set and enteral feeding pump providing an alternate embodiment of the anti-freeflow mechanism of the present invention; and
FIG. 7C shows a close-up, cross-sectional view of yet another embodiment of the anti-freeflow mechanism of the present invention. DETAILED DESCRIPTION
Reference will now be made to the drawings in which the various elements of the present invention will be given numeral designations and in which the invention will be discussed so as to enable one skilled in the art to make and use the invention. It is to be understood that the following description is only exemplary of the principles of the present invention, and should not be viewed as narrowing the pending claims.
Referring to FIG. 1A, there is shown a top view of an enteral feeding system taught in U.S. Patent No. 5,720,721. The enteral feeding system, generally indicated at 4, has a delivery set 8 including an intake (upstream) tube 10 and an output (downstream) tube 14 connected together by a pair of connectors 18 and a pump tubing segment within an enteral feeding pump 20. The position of the pump tubing segment disposed inside of the pump 20 is represented by the dashed lines 16.
The enteral feeding pump 20 includes a housing 24 with a conventional motor unit, generally indicated at 28. The motor unit 28 includes a rotor 30 with a plurality of peristaltic rollers 34 disposed about an exterior of the rotor to move liquid through the enteral feeding pump 20. The rotor 30 is connected by a shaft 32 to a motor (not shown) . The section 38 of the pump tubing segment 16 is disposed about the rotor 30 and rollers 34 and is usually made of a flexible silicone material. Rotating the rotor 30 in the direction indicated by the arrows directionally squeezes the tube section 38 and causes solution to be pushed through the output tube 1 .
Also shown in FIG. 1 is an air detector 40 provided in a proximal position (upstream) from the motor unit 28 along the intake tube 10 to warn medical personnel of an empty supply container or a large bubble in the infusion set.
In addition to these elements, the enteral feeding pump 20 of the present invention includes a pair of pressure sensors 50. In a preferred embodiment, two pressure sensors 50a and 50b are disposed along the pump tubing segment 16 adjacent the intake/output tubes to 1) ensure that the tubes are properly mounted in the pump 20; 2) monitor any changes in viscosity which are significant enough to alter the amount of liquid moved by each rotation or partial rotation of the rotor 30; and 3) detect any occlusions in the intake tube 10 or the output tube 14 of the delivery set 8. A retention plate 54 (FIG. 1) is attached to the housing 24 by a screw 58 to hold the pressure sensors 50a and 50b in place.
While the pressure sensor system of U.S. Patent No.5, 720, 721 was a significant improvement over the art, it does have limitations. Specifically, the pressure sensors are relatively expensive and the accuracy depends on the proper loading of the tube in the pump. Additionally, the air detector used ultrasonic energy and ultrasonic sensors are relatively expensive. Furthermore, as the health care professional or patient loaded the pump, he or she could effect the relative stretching of the tube as it was wrapped around the rotor of the pump. This, in turn, could effect the strain detected by the pressure sensors . In addition to the above, the pump required some sort of anti free flow mechanism to prevent solution from running through the infusion set when the tube was not securely engaging the pump rotor. Thus, a pinch clip occluder, as shown in FIG. IB at 96 was taught in U.S. Patent No. 5,704,584. While the pinch clip occluder shown is highly effective, it is relatively expensive compared to the cost of the infusion set.
Turning now to FIGs . 2A and 2B there are shown a top perspective view and a bottom perspective view of a feeding set adaptor, generally indicated at 100, which improves upon the prior art. The feeding set adaptor has a connector portion 104 having a first connector 108 and a second connector 112. The first connector portion 104 also preferably has a small handle 116 which can be used to pull the feeding set adaptor 100 from a pump if necessary.
The first connector 108, a functional proximal end 108a which engages the functional distal end of an inflow line (not shown) of an infusion set. The opposing end of the infusion line is typically disposed in communication with a fluid container which holds the solution being delivered to the patient. The first connector 108 will typically be approximately the same diameter as the inflow tube, and the inflow tube is mounted on the first connector by being stretched over the distal end 108a of the connector.
The first connector 108 also has a functional distal end 108b. The distal end 180b is preferably configured with an annular barb 108c and a neck portion 108d positioned proximally from the annular barb. The annular barb 108c and neck portion 108d are used to secure a pump engagement portion of the infusion set, which is discussed below regarding FIG. 2C. As shown in FIG. 1, the distal end 108b of the first connector 108 has conduit 120 which is generally triangular .
Disposed within the first connector 108 is a sample cell 124. As will be discussed in additional detail below, the sample cell 124 is used in conjunction with an optical sensor (not shown) to optically determine the presence of air bubbles within the conduit 120. The sample cell 124 is preferably triangular and has sidewall which are offset from one another at an angle of between about 47-70 degrees. In a presently preferred embodiment, the sample cell 124 is made with a wall which forms an equilateral triangle with two sidewalls being disposed at an angle of about 50 to 60 degrees. Such an angle allows light emitted from the optical sensor to be refracted in a first direction if the conduit 120 is filled with liquid, and a second direction if the conduit has any appreciable amount of air. The refracted light, or relative absence thereof, indicates the relative size of the air bubble. A more detailed discussion regarding bubble detection is found in U.S. Patent Application Serial No. 09/836,840 (Co-filed herewith and identified as Attorney Docket No. 0906. ZEVX. PT) which is expressly incorporated herein.
Disposed functionally distally (i.e. downstream) from the distal end 108b of the first connector 108 is a first tube engagement member 130. The first tube engagement member 130 preferably includes a wall 132 having generally U-shaped opening 134 which is sized to receive the pump engagement portion of the infusion set. The first tube engagement member 130 also preferably includes a pair of flanges 138 which extend inwardly to partially obstruct the opening and to form a recess which receives a collar (see FIG. 2C) of the pump engagement portion of the infusion set. The pump engagement portion of the infusion set, which is generally indicated at 200 in FIG. 2C includes an elongate tube portion 204. The tube portion 204 is preferably a flexible tube made from a medical grade material, such as silicone. Such tubes are commonly used in enteral feeding pumps.
Unlike most enteral feeding pump tubes, however, the tube portion 204 has a first fitting 208 disposed at a functionally proximal end (i.e. upstream). The first fitting 208 is preferably used by a machine to secure the tube portion 204 and to attach a proximal end 204a of the tube to the distal end 108b of the first connector 108.
Disposed distally from the first fitting 208 is a first abutment member 212, which is preferably in the form of a collar 216. (In light of the present disclosure, those skilled in the art will appreciate that numerous other abutment configurations could be used to secure the tube portion 204 as described) . The abutment member 212 in particular, and the collar 216 specifically, are designed to nest in the recess 142 against the wall 132 of the first tube engagement member 130. When nested in the recess, the tube portion 204 which is proximal to the collar 216 is held taut between the first tube engagement member 130 and the first connector 108.
When the pump engaging portion 200 of the infusion set is attached to the distal end 108b of the first connector 108, it is stretched slightly until the collar 216 is slightly passed the flanges 134 of the first tube engagement member 130. The tube portion 204 is then moved between the flanges 134 and the tube released so the contraction of the tube pulls the collar 216 into the recess 142.
Disposed distally from the first tube engagement member 130 is a second tube engagement member 150. As with the first tube engagement member 130, the second tube engagement member preferably includes a wall 152 with a generally U-shaped opening 154. which is sized to receive the pump engagement portion of the infusion set.
The second tube engagement member 150 also preferably includes a pair of flanges 158 which extend inwardly to partially obstruct the opening and to form a recess 162 which receives an abutment member 220, which is preferably in the form of a collar 224 (FIG. 2C) . (Those skilled in the art will appreciate that other abutment members such as arms, nubs or flanges could also be used) . As shown in FIG. 2B, the recess 162 preferably faces the recess 142 in the first tube engagement member and works with the collar 224 to prevent the portion of the tube portion 204 disposed proximally adjacent to the collar from being stretched to any significant degree when the central working portion 230 of the pump engaging portion 200 of the infusion set. Likewise, when the pump rotor rotates, the stretching of the tube portion 204 proximally from the collar 224 is minimized.
Because the proximal collar 216 prevents proximal movement and the distal collar 224 prevents distal movement, the portion 234 of the tube disposed therebetween is held against movement, this portion forms a relatively isolated monitoring portion 234.
To properly determine the flow through an infusion set, and to properly determine the presence of occlusions in an infusion set, it is advantageous to monitor pressure within the infusion set. This can be accomplished either by pressure sensors, such as those discussed in U.S. Patent No .5 , 720 , 721, or by an optical detector as discussed in co-pending U.S.
Patent Application No. 09/836,852 (Filed concurrently herewith and identified as attorney docket no. 0908.ZEVX.PT, and which is expressly incorporated herein) . As is explained more fully in the co-pending application, the pressure in the infusion set can be determined by having, the tube occlude light in an optical sensor. As the tube expands due to increased pressure or contracts due to a vacuum caused by occlusions, etc., the amount of light which is received by the optical sensor changes, thereby indicating the change in pressure in the tube. Using the diameter of the tube to determine pressure can provide highly accurate readings. However, the accuracy of such readings is diminished if the tube is being stretched inconsistently because having the tube under tension will change the extent to which it expands and contracts due to pressure changes. This is resolved in the present invention by the first and second tube engagement members 130 and 150 and the abutment members 212 and 220 (collars 216 and 224) . These structures interact so that the monitoring portion 234 is held relatively unstretched, regardless of tension from either side. Because most of the tension will occur due to loading the central working portion 230 of the pump engagement portion 200 and rotation of the pump rotator, the second tube engagement member 150 is more critical than the first pump engagement portion. Thus, it will be appreciated that the first pump engagement portion 130 could be omitted while maintaining most of the benefits of the present invention.
The feeding set adaptor 100 also includes a third tube engagement member 170. The third tube engagement member preferably includes a wall 132 defining a generally U-shaped opening 174 which is sized to receive the pump engagement portion of the infusion set. The third tube engagement member 170 also preferably includes a pair of flanges 178 which extend inwardly to partially obstruct the opening and to form a recess 182 which receives an abutment member 240, which is preferably in the form of a collar 244 (FIG. 2C) .
As shown in FIG. 2B, the recess 182 preferably faces in the same direction as the recess 162 in the second tube engagement member 150. When the pump engaging portion 200 of the infusion set is properly loaded, the collars 224 and 244 are disposed in recesses 162 and 182. This substantially isolates the central working portion 230 and prevents rotation of the pump rotor from causing tension either upstream or downstream from the collars 224 and 244, respectively. The feeding set adaptor 100 further comprises a fourth tube engagement member 186. The fourth tube engagement member 186 preferably includes a wall having a generally U-shaped opening 188. A pair of flanges 190 are disposed adjacent the U-shaped opening to partially obstruct the opening and to form a recess 192. The pump engaging portion 200 of the infusion set includes an abutment member 250 in the form of a collar 254 which is configured to nest in the recess 192.
The recess 192 of the fourth tube engagement member 186 faces the same direction as first tube engagement member 130 and the third and fourth tube engagement members act together in the same manner as the first and second engagement members to isolate a second monitoring portion 260 on the tube 204. Thus, the infusion pump is able to optically monitor both the upstream pressure between the first and second engagement members 130 and 150, and the downstream pressure between the third and fourth engagement members. Thus, the pump can readily determine if an occlusion in the infusion set is inhibiting delivery of solution to the patient.
The feeding set adaptor 100 also includes an anti- freeflow mechanism 300. As shown in FIGs. 2A and 2B, the anti-freeflow mechanism 300 is in the form a small ball 304 which is attached to the proximal (i.e. upstream) end 112a of the second connector 112 by a small wall 308. The wall 308 is configured to provide minimal resistance to flow of liquid into the proximal end 112a of the second connector 112. In order to prevent freeflow through the infusion set, the anti-freeflow mechanism 300 is inserted into the distal end 204b of the tube portion 204. The tube portion 204 is then advanced until the distal end 204b passes over an annular barb 112c and rests on the neck 112d of the second connector 112. A second fitting 268 on the tube portion 204 is typically used so that a machine can readily mount the distal end
204b of the tube portion 204 on the proximal end 112a of the second connector 112.
Once the tube is in place, the small ball 304 will prevent solution flow through the tube portion 204 unless the solution is under sufficient pressure.
Thus, the small ball 308 will prevent flow through the tube portion 204 if the solution is simply subject to gravity. However, if the solution is placed under sufficient pressure, the flexible material (typically silicone) of the tube portion 204 will expand and allow solution to flow past the small ball 308. This is accomplished as the pump drives solution through the infusion set. If the pump is not properly engaging the central working portion 230 of the tube portion 204, there will not be enough pressure to bypass the anti-freeflow mechanism 300. In other words, unless the pump is in control of the fluid flow, no fluid will flow through the infusion set and a freeflow situation will not develop. While the workings of the anti-freeflow mechanism 300 are discussed in additional detail below, numerous different embodiments of anti-freeflow mechanisms which can be used with the present invention are discussed in U.S. Patent Application Serial No.09/569, 332, and co-flied U.S. Patent Application Serial No. 09/836,850 (identified as attorney file 0905.ZEVX. CI) , both of which are expressly incorporated hearin .
Once the solution in the tube portion 204 has been driven past the anti-freeflow mechanism 300, the solution passes into the proximal end 112a of the second connector 112. The distal end (downstream) 112b of the second connector 112 is disposed in engagement with a patient portion of the infusion set (not shown) . Typically, the patient portion of the infusion set is slid over the second connector 112 and retained in a frictional engagement. It can, however, be attached by other means .
Turning now to FIG. 3, there is shown a bottom view of an enteral feeding set adaptor 100 having the pump engaging portion 200 of the infusion set disposed therein for mounting on an infusion pump in accordance with the principles of the present invention. The central working portion 230 of the pump engaging portion 200 extends outwardly from the feeding set adaptor 100 in a loop. In the prior art configurations, the portion of the infusion set which engages the pump rotor can be stretched unevenly as it is mounted on the pump. This can interfere with monitoring of pressure within the infusion set. Additionally, stretching the tube and wrapping it around the pump rotor can take some coordination.
In contrast, the feeding set adaptor 100 and pump engaging portion 200 of the infusion set is loaded by simply engaging the far side of the loop 230a against the pump rotor and pulling the feeding set adaptor 100 until it can be inserted in the pump. With such a configuration, the risk of the central working portion 230 being stretched unevenly is virtually eliminated. Additionally, it takes very little coordination to properly load the feeding set adaptor 100 in the pump.
The user simply loops the end 230a of the looped central working portion 230 over the rotor and pulls back on the feeding set adaptor 100 until it is in alignment with a cavity on the pump, and releases the feeding set adaptor.
Turning now to FIG. 4, there is shown a fragmented perspective view of an infusion set, generally indicated at 310 and a perspective view of a feeding set adaptor 100 and an enteral feeding pump, generally indicated at 320, made in accordance with principle of the present invention. The infusion set 310 includes an inflow tube 314 which is typically connected to a solution container (not shown) , such as a plastic bag holding enteral feeding solution, and an outflow tube 318, which is generally connected to an adaptor (not shown) which engages a balloon catheter which traverses the abdominal wall of the patient.
The inflow tube 314 is connected to the pump engaging portion 200 of the infusion set 310 by the first connector 108. As discussed above, the solution passing through the inflow tube 314 and the first connector 108 passes through the sample cell 124. Due to the configuration of the feeding set adaptor 100, the sample cell 124 nests in a channel 324 of the infusion pump 320. A portion of the channel 324 defines a housing 328 which is preferably made of a generally translucent plastic. The housing 328 serves the dual purpose of protecting an optical sensor (not visible in FIG. 4) from liquids, and of refracting light which is emitted and received by various parts of the optical sensor. As the solution passes through the sample cell 124, the optical sensor sends light through the housing 328 and sample cell 124. If liquid is in the sample cell 124, most of the light will travel in such a path that it is not reflected back to an optical detector. The sample cell 124 is specifically designed so that it always sends some light to the optical detector to provide an integrity check of the optical sensor. If a bubble is present, however, a light emitted by the optical sensor is refracted to the optical detector. The amount of light which is refracted gives a reliable indication of whether a bubble is present, and the size of the bubble. If the bubble exceeds desired thresholds, the pump 320 can generate an alarm. The alarm may be audible, or simply appear on a display screen 332 on the pump 320. Once the solution has passed through the sample cell 124, it passes out of the first connector 108 and into the monitoring portion 230 of the pump engaging portion 200 of the infusion set 310. The monitoring portion 234 is disposed between the first and second tube engagement members 130 and 150, and is disposed in a distal section 324a of the channel 324.
Disposed in the walls of the distal section 324a of the channel 324 is an optical sensor (not shown) . The optical sensor sends light between an optical signal emitter and an optical signal detector. As the monitoring portion 234 of the tube is disposed in the distal section 324a of the channel 324, it is positioned to partially obstruct the light flow between the optical signal emitter and the optical signal detector. The diameter of the monitoring portion 234 changes as pressure changes within the tube. The change in diameter of the monitoring portion 234 changes the amount of light which is detected by the optical detector and allows the pump 320 to determine pressure within the monitoring portion without direct contact. For example, if the inflow line 314 of the infusion set 310 were to be kinked or otherwise occluded, flow through the inflow line would be reduced. As the pump rotor 340 of the infusion pump 320 rotates, it will develop a vacuum upstream from the rotor. Because the inflow line 314 is occluded, the vacuum created by the rotation of the rotor 340 will be greater in magnitude and will remain longer than if flow through the inflow tube were not obstructed. The vacuum will cause the monitoring portion 234 of the pump engaging portion 200 to collapse to a greater degree and remain in a collapsed state for a longer period of time. The optical sensor detects the collapse because more light will be detected by the optical detector and for a longer period of time. The pump 320 monitors the readings of the optical sensor. If the readings of the optical detector fall outside of a predetermined range, the pump 320 will generate an alarm indicating the presence of an occlusion. It may also automatically stop the pump 320 until the occlusion situation has been resolved. A more detailed discussion of the interaction between the optical sensor and the monitoring portion 234 of the infusion set 310 is set forth below. Additionally, co-filed U.S. Patent Application Serial No. 09/836,852 (identified as Attorney Docket No. 0908. ZEVX. PT) contains a detailed discussion of numerous different applications of such a pressure sensor and is expressly incorporated herein.
As the solution passes out of the monitoring portion 234, it passes into the central working portion 230 of the pump engaging portion 200 of the infusion set 310. The central working portion 230 is engaged by a plurality of rollers 344 on the pump rotor 340. As the rotor 340 rotates, the rollers 344 pinch off sections of the tube and advance theoretically known volumes of solution with each rotation. (The actual volumes moved are partially dependent on the pressures on the solution both upstream and downstream from the rotor 340) . By controlling the number of rotations of the rotor 340, and making modifications for detected pressures, the pump 320 can deliver a known volume of solution to the patient .
Once the solution has been moved downstream of the rotor 340, it passes into the second monitoring portion 260 which is disposed between the third and fourth tube engagement portions 170 and 186. The second monitoring portion 260 rests in a channel 354 in the pump 320 which is preferably disposed parallel to channel 324. The channel 354 also has an optical sensor which functions in substantially the same manner as the sensor discussed in association with the monitoring portion 234. The only signficiant difference between the two is that which the monitoring portion 234 will generally collapse due to vacuum created by the pump rotor 340 and upstream occlusions, the second monitoring portion 260 will generally expand due to solution being forced down stream by the pump rotor 340 and any occlusions downstream which inhibit the downstream flow of solution.
Once the solution passes out of the second monitoring portion 260, it must flow around the anti- freeflow device 300. As mentioned above, gravity alone is insufficient to develop flow around the anti- freeflow device 300. However, the rotation of the pump rotor 340 pushes solution downstream with sufficient force that the tube 204 adjacent the anti- freeflow device will expand and create a channel around the ball 304, thereby allowing the solution to flow down stream to the patient.
Once past the anti-freeflow device 300, the solution flows through the second connector 112 and into the outflow portion 318 of the infusion set 310 which delivers the solution to the patient.
Turning now to FIGs. 5 and 5A, there are shown close-up, cross-sectional views of the feeding set adaptor 100, flexible tubing 204 of the pump engaging portion 200 and a portion of the enteral feeding pump 320 relating to the pressure monitoring mechanism associated with feeding set adaptor. The enteral feeding pump 320 has two channels 324 and 354 which receive the feeding set adaptor 100.
As shown in FIGs. 5 and 5A, the monitoring portion 230 of the flexible tubing 204 of the pump engaging portion 200 is disposed in the first chan Disposed on opposing sides of the first channel 324 is an optical sensor 400. The optical sensor includes a optical signal emitter 404 and an optical signal detector 408. Each is provided with leads 412 for communication with the enteral feeding pump.
In response to an electrical signal from the pump 324, the optical signal emitter 404 emits light energy, indicated by dashed line 420. Those skilled in the art will appreciate that various wavelengths of light may be used. Currently, it is anticipated that infrared light will be preferred.
The flexible tube 204 forming monitoring portion 230 is positioned to obstruct some of the light. The extent to which the light is obstructed, of course, depends on the diameter of the flexible tube 204 in the monitoring portion 230. This diameter, depends on the pressure within the tube. Thus, by monitoring the amount of light which is obstructed, the voltage or other readings of the sensor correlates with the pressure inside of the tube.
In a preferred embodiment, the flexible tube 204 forming the monitoring portion 230 is disposed so that it always obstructs some light, but does not obstruct all light flow between the optical signal emitter and the optical signal detector. This can be used to verify the integrity of the sensor and proper loading of the tubing. If the optical signal detector 408 gives the maximum voltage reading, the tubing 204 is not loaded properly. If, in contrast, no optical signal is received by the optical signal detector 408, the sensor 400 is defective and must be serviced or replaced.
Turning specifically to FIG. 5A, there is shown a view similar to that of FIG. 5. However, with respect to the monitoring portion 230, the diameter of the tube 204 has decreased. This typically occurs with each rotation of the pump rotor (FIG. 4) as a temporary vacuum is created as solution is forced through the infusion set. The extent of the vacuum and its duration, however, is related to the presence of occlusions, and/or the viscosity of the solution. The sensor 400 detects the extent of the reduced diameter of the tube 204 in the monitoring portion 230 by the amount of light received by the optical signal detector 408. The optical sensor 400 is thereby able to determine the negative pressure within the tube.
The pump 320 is then able to make adjustments to rotor rotations to ensure accurate volume delivery. It can also detect an occlusion that should be resolved and generate an alarm. The pump 320 also has a second optical sensor 400' which is disposed along the second monitoring portion 260 which is down stream from the pump rotor (FIG. 4) . The sensor 400' has an optical signal emitter 404 and an optical signal detector 408 which have leads 412 for communicating with the pump. The sensor 400' operates in substantially the same manner as the optical sensor 400 and is therefor not discussed in detail .
One difference between the practical applications of the sensor 400' and sensor 400 is that, because the sensor 400' is downstream, the sensor 400' will detect pressure increase in the second monitoring portion 260 with each rotor rotation, instead of the pressure decreases associated with the first monitoring portion 230. Thus, as the rotor (FIG. 4) rotates, the pressure in the second monitoring portion 260 will increase. As shown in FIG. 5A, the increase in pressure causes the diameter of the second monitoring portion to increase and decreasing the amount of light received by the optical signal detector 408.
The sensor 400' and monitoring portion 260 can be configured in a variety of ways to achieve the goals of the present invention. In a preferred configuration, the tube 204 is positioned within the sensor such that it will always occlude some light, but will never fully occlude all light from the optical signal emitter 404 to the optical signal emitter 408. Thus, a full voltage reading indicates that the tube 204 forming the monitoring portion 260 is not properly loaded. A zero reading indicates that the sensor 400' has malfunctioned and must be serviced or replaced.
Between the two extremes is a range of values which correlate with acceptable pressures which the pump 320 can use to ensure accuracy in volumetric delivery. This is also a threshold which indicates a pressure which exceeds acceptable pressure in the infusion set. If the threshold is surpassed, the pump 320 will generate an alarm and warn the user that the infusion set is obstructed.
Those skilled in the art will appreciate that the tube 204 and sensor 400' could be disposed in communication such that the threshold pressure occludes all light and therefore generates an alarm. While such a configuration meets the requirements of generating an alarm and/or shutting off the pump 320 when the pressure is too high, it has the disadvantage of not distinguishing between a faulty sensor in the pump and an unacceptably high pressure in the infusion set .
Those skilled in the art will also realize that numerous modifications could be made to the presently preferred embodiment disclosed herein. The sensors need not be disposed adjacent each other and could be disposed in other locations along an infusion set. FIGs. 6 and 6A show a close-up, cross-sectional view of the adaptor and the enteral feeding pump portions relating to the detection of air bubbles passing through the infusion set. Specifically, the sample cell 124 is disposed in the channel 324 of the pump. The channel 324 has a portion 324b which is defined by a sloped housing 430. The sloped housing 430 is preferably formed of a clear plastic, such as ABS and has walls 430a and 430b which are offset from one another at an angle of between about 45-100 degrees (most preferably about 60 degrees) , and preferably between 40 and 67.5 degrees from horizontal, and a base 432. The housing also preferably has a flanged portion 434. The housing 430 helps both with bubble detection as explained below, and prevents water or other hazzards from entering the pump 320.
Disposed adjacent the housing 430 is an optical sensor 440. The optical sensor 440 has an optical signal emitter 444 and an optical signal detector 448 which are disposed on opposing sides of the housing 430. Leads 452 are provided for the optical sensor 440 and pump 320 to send electronic signals to one another.
The sample cell 124 is placed in the channel 324 so that it is spaced away from the housing 430 slightly and forms an air chamber 458 between the sample cell and housing. While it is preferred that the conduit 460 formed by the sample cell 124 has a cross-section which forms an inverted equilateral triangle and the sample cell 124 preferably has two walls disposed at 60 degrees from one another, the walls defining the conduit need not form a triangle. As shown in FIG. 6, the walls have a base 464 which is formed at the bottom of the inverted triangle. Additionally, the top wall 468 could be curved or vaulted to provide the conduit with a diamond shape. Also, as set forth in more detail in U.S. Patent Application Serial No. 09/836, 840 (identified as
Attorney Docket No. 0906. ZEVX. PT, which is expressly incorporated herein) , numerous different configurations can be used. It is most desirable, however, that the sidewalls be disposed at an angle less than normal to the plane along which the light is emitted to refract the light back to an optical detector when air is present in the sample cell.
In use, light is emitted by the optical signal emitter 444 and is refracted by a sidewall of the housing 430 and again by the air of the air chamber 458. The light is again refracted as it enters into the sidewall 430a of the housing. If the conduit 460 is filled with solution, the light undergoes very little refraction as it passes from the sidewall 430a of the housing 430 into the solution. Thus, the light travels in a generally straight path which prevents the light from contacting the optical signal receiver 448 as shown by the dashed line in FIG. 6.
If, however, the conduit 460 is filled with air, the difference indices of refraction of the plastic sample chamber 124 and the air in the conduit 460 causes the air to be refracted to a much greater degree as shown by the upper dashed line in FIG. 6A. The light is then refracted again as it passes from the air in the conduit to the opposing sidewall 430b, through the air chamber 458 and through the housing 430. The refraction is such that the light is directed to the optical signal detector 448. If an air bubble is present in the conduit 460, it will direct an increased amount of light to the optical signal detector 448. The amount of light refracted to the optical signal detector 408 is proportional to the size of the air bubble. Thus, the voltage reading obtained from the optical signal detector 448 is proportional to the size of the bubble.
The base 464 of the sample cell 124 assists in the important role of integrity checking the optical sensor 440. The base 464 is positioned so that it will always allow some light through to impact the optical signal detector 448 as shown by the lower dashed line in FIG. 6A. Thus, if the optical signal detector 448 indicates a reading of zero, an alarm can be generated indicating that the sensor 440 has failed. Likewise, the refraction of light is controlled so that too high of a reading indicates that the sample cell 124 has not been properly loaded in the channel 324.
Turning now to FIGs. 7 and 7A, there are shown close-up, cross-sectional views of the feeding set adaptor 100 and the pump engaging portion 200 of the infusion set 310 as they relate to the anti-freeflow mechanism 300 of the present invention. It is important to prevent an infusion set from providing uncontrolled solution to the patient. While many enteral feeding systems have roller clamps or other pinch clip occluders, most devices do not affirmatively prevent fluid flow when the pump is not controlling the flow. In contrast, the anti-freeflow mechanism 300 only allows fluid flow when the pump is actively driving solution through the system.
The anti-freeflow mechanism shown in FIGs. 7 and 7A is a small substantially ball-shaped member 304 which is sized slightly larger than the inside diameter of the flexible tube 204 which forms the pump engaging portion 200 of the infusion set 310. As such, the ball-shaped member 304 prevents fluid flow under gravity pressures. If, however, a pressure well above that caused by gravity is developed in the flexible tube 204, the flexible tube will expand and develop a channel 480 about the exterior of the ball- shaped member 304. (It will be appreciated that other shapes may also be used) .
The channel 480 is opened each time the pump rotor drives solution through the pump engaging portion 200 of the infusion set 310 and allows solution to flow downstream. Unlike other clamps which are manually controlled or which open by closing of the pump housing, the configuration is advantageous because it will not allow a freeflow condition to develop, even if the feeding set adaptor 100 is properly mounted in the pump 320 and the pump engaging portion 200 of the infusion set 310 has simply been pulled out of engagement with the pump rotor.
Turning now to FIG. 7B, there is shown a cross- sectional view of the adaptor 100, pump engaging portion 200 of the infusion set 310 and enteral feeding pump 320 providing an alternate embodiment of the anti-freeflow mechanism of the present invention. While the embodiment discussed with respect to FIGs. 7 and 7A is presently preferred, there may be situations iri which it is not desired to force the solution to open a channel around the anti-freeflow mechanism. In such situations, the channel can be opened by interaction of a pump cover 500, the anti-freeflow mechanism 300 and the channel 354 of the pump 320. The cover 500 preferably has an engagement member 504 which is configured to forcefully engage the flexible tube on the opposite side of the tube from the anti- freeflow mechanism. The channel 354 also may have a stop 510 which engages the outside of the flexible tube 204 opposite the anti-freeflow mechanism 300.
As the flexible tubing 204 gets compressed between the engagement member 504 and the anti-freeflow mechanism 300 and between the stop 510 and the anti- freeflow mechanism, the flexible tubing will bow outwardly along the sides of the anti-freeflow mechanism 300 and form channels for the solution to flow around the anti-freeflow mechanism. Thus, once the cover 500 is closed and secured, solution flow passed the anti-freeflow mechanism 300 can occur regardless of whether the pump rotor 340 is properly engaging the pump engaging portion 200 of the infusion set 310. Turning now to FIG. 7C, there is shown a close-up, cross-sectional view of yet another embodiment of the anti-freeflow mechanism 300' of the present invention. Instead of using a ball-shaped member 304 inside of the tube, the embodiment shown in FIG. 7C shows a flap 304' which is disposed in the connector 112. The flap is configured to substantially prevent fluid flow through the connector if pressures are equal to or less than typically encountered due to gravity. If a desired pressure threshold is passed, the flap 304' is forced open and allows solution to flow down stream. Those skilled in the art will appreciate that the flap 304' could be configured to remain open once deflected by the solution pressure, or could be mounted such that the flap 304' returns to its original position once the solution pressures are insufficient to hold the flap open.
Thus there is disclosed an improved feeding set adaptor. The adaptor enables the integration of the various functions discussed above, and provides improved pressure monitoring, anti-freeflow and bubble detection at a price well below the systems of the prior art. Additionally, the feeding set adaptor increases the ease of loading and unloading the tube engaging portion of the infusion set. While numerous different embodiments of the present invention have been disclosed, those skilled in the art will appreciate numerous modifications which can be made without departing from the scope and spirit of the present invention. The appended claims are intended to cover such modifications.

Claims

What is claimed is:
1. A feeding set adaptor comprising: a first connector configured for attachment to an inflow line of an infusion set and a central pump engaging portion of an infusion set; a second connector configured for attachment to an outflow line of an infusion set; and an anti-freeflow mechanism disposed in communications with the one of the first connector and the second connector.
2. The feeding set adaptor according to claim 1, wherein the anti-freeflow mechanism is attached to and spaced apart from one of the first connector and the second connector.
3. The feeding set adaptor according to claim 1, wherein the anti-freeflow mechanism comprises a generally ball-shaped member configured for disposition in the tubing of an infusion set. 4. The feeding set adaptor according to claim 3, wherein the ball-shaped member is attached to one of the first connector and the second connector and spaced away from the connector to which the ball- shaped member is attached so that a flow channel may be formed around the ball-shaped member and into the connector to which the ball-shaped member is attached.
5. A solution delivery system for disposal on an infusion pump comprising the feeding set adaptor according to claim 1, and further comprising an inflow line, a pump engaging portion, and an outflow line attached to the feeding set adaptor.
6. The solution delivery system according to claim 5, wherein the anti-freeflow mechanism is disposed in one of the inflow line, pump engaging portion and outflow line.
7. The solution delivery system according to claim 6, wherein the anti-freeflow mechanism is attached to the second connector and disposed in the pump engaging portion of the infusion set.
8. The solution delivery system according to claim 7, wherein the outside diameter of the anti-
5 freeflow mechanism is slightly larger than the inside diameter of the pump engaging portion of the infusion set.
9. The solution delivery system according to claim 5, wherein the anti-freeflow mechanism is a
10 generally ball-shaped member.
10. The solution delivery system according to claim 5, wherein the pump engaging portion comprises at least one monitoring portion for optically monitoring pressure within the infusion set.
15 11. The solution delivery system according to claim 10, wherein the pump engaging portion further comprises at least one abutment member for engaging the feeding set adaptor to minimize movement of the monitoring portion when the pump engaging portion is
■20 worked by a pumping mechanism.
12. The solution delivery system according to claim 11, further comprising an optical sensor disposed adjacent to the monitoring portion for determining pressure in the monitoring portion.
25 13. The solution delivery system according to claim 12, wherein the optical sensor comprises an optical signal emitter and an optical signal emitter and an optical signal detector, and wherein at least a portion of the monitoring portion is disposed between
30 the optical signal emitter and the optical signal detector.
14. The solution delivery system according to claim 13, wherein the monitoring portion is disposed between the optical signal emitter and the optical 35 signal detector, so that it always occludes some light flow between the optical signal emitter and the optical signal detector.
15. The solution delivery system according to claim 13, wherein the monitoring portion is disposed between the optical signal emitter and the optical signal detector, so that it always allows some light flow between the optical signal emitter and the optical signal detector.
16. The solution delivery system according to claim 11, wherein the feeding set adaptor has at least one tube engaging member and wherein the abutment member of the pump engaging portion engages the tube engagement member of the feeding set adaptor to limit movement of the pump engagement portion.
17. The solution delivery system according to claim 16, wherein the at least one tube engaging member defines a recess, and wherein the abutment member comprises a collar configured for resting in the recess.
18. The solution delivery system according to claim 16, wherein the at least one tube engagement member comprises a first tube engagement member and a second tube engagement member disposed adjacent to each other with the monitoring portion extending therebetween.
19. The solution delivery system according to claim 18, wherein the pump engagement portion has a first abutment member disposed to engage the first tube engaging member and a second abutment member disposed to engage the second tube engaging member, the two abutment members being spaced apart and a distance therebetween constituting the monitoring portion of the pump engaging portion of the infusion set.
20. The solution delivery system according to claim 18, wherein the at least one tube engagement member further comprises a third tube engagement member and a fourth tube engagement member disposed adjacent to each other, and the pump engaging portion of the infusion set forming a second monitoring portion extending between the third tube engagement member and the fourth tube engagement member .
21. The solution delivery system according to claim 16, wherein the at least one tube engaging member and the at least one monitoring portion comprise a first monitoring portion and at least one tube engagement configured for disposition upstream from a pump rotor, and a second monitoring portion and at least one tube engagement member configured for disposition downstream from a pump rotor.
22. The feeding set adaptor according to claim 1, further comprising a sample cell formed as part of the adaptor. 23. The feeding set adaptor according to claim 22, wherein the sample cell has a pair of side walls disposed at an angle between about 45 and 100 degrees from one another.
24. The feeding set adaptor according to claim 23, wherein the sample cell defines a conduit having at least two sides which are disposed at an angle of about 50 to 60 degrees from one another.
25. The feeding set adaptor according to claim 24,. wherein the conduit has a cross-section which is an equilateral triangle.
26. The feeding set adaptor according to claim 25, wherein the conduit has a cross-section which is an inverted equilateral triangle, the sides extending downwardly and inwardly. 27. The feeding set adaptor according to claim
24, wherein the conduit has a cross-section which is diamond shaped.
28. The feeding set adaptor according to claim
22, wherein the sample cell has an outer wall which extends toward point, and a generally linear base extending outwardly from the point and disposed to
Figure imgf000040_0001
Figure imgf000040_0002
sample cell configured for optically detecting air bubbles within the sample cell .
37. The feeding set adaptor according to claim
36, wherein the sample cell comprises at least two side walls disposed at an angle of between about 45 and 100 degrees to one another.
38. The feeding set adaptor according to claim
37, wherein the sample cell comprises an equilateral triangle, with sidewalls disposed at an angle of about 50 to 60 degrees from one another.
39. The feeding set adaptor according to claim
38, wherein the sample cell further comprises a base disposed at one corner of the equilateral triangle.
40. The feeding set adaptor according to claim 36, wherein the sample cell defines a conduit which has a cross-section of an inverted equilateral triangle .
41. A solution delivery system including the feeding set adaptor according to claim 36, and further comprising an optical sensor disposed adjacent the sample cell.
42. The solution delivery system according to claim 41, wherein the optical sensor includes an optical signal emitter and an optical signal detector placed generally on opposing sides of the sample cell.
43. The solution delivery system according to claim 41, wherein the sample cell configured such that when disposed between the optical signal emitter and the optical signal detector, the sample cell will dispel some light emitted by the optical signal detector so that said light does not reach the optical signal detector.
44. The solution delivery system according to claim 41, wherein the sample cell is configured so that some light from the optical signal emitter will always reach the optical signal detector when the sample cell is disposed between the optical signal emitter and the optical signal detector.
45. The solution delivery system according to claim 44, wherein the sample cell comprises a base portion configured to channel light emitted by the optical signal emitter to the optical signal detector regardless of whether the sample cell is full or air or liquid.
46. The solution delivery system according to claim 41, wherein the system further comprises a housing disposed between the optical signal sensor and sample cell .
47. The solution delivery system according to claim 46, wherein the housing has a pair of sidewalls disposed at an angle of between about 45 and 100 degrees relative to one another.
48. The solution delivery system according to claim 47, wherein the housing and the sample cell each have side walls disposed at an angle of about 60 degrees to one anther and wherein said sidewalls of the sample cell are disposed in parallel to the sidewalls of the housing.
49. The solution delivery system according to claim 46, wherein the housing and the sample cell are spaced apart to define an air chamber therebetween.
50. The solution delivery system according to claim 46, wherein the sample cell has a base and wherein the housing has a base disposed generally parallel to the base of the sample cell. 51. The solution delivery system according to claim 46, wherein the optical sensor and the housing are formed as part of an infusion pump.
52. The feeding set adaptor according to claim
36, wherein the feeding set adaptor has a second connector for connecting the pump engaging portion to an outflow line of an infusion set.
53. The feeding set adaptor according to claim 36, wherein the adaptor further comprises at least one tube engagement member configured for engaging a pump engaging portion of an infusion set. 54. A solution delivery system having the feeding set adaptor according to claim 53, and further comprising a flexible tube attached to the feeding set adaptor, the flexible tube forming a pump engaging portion of an infusion set. 55. The solution delivery system according to claim 54, wherein the pump engaging portion of the infusion set has an abutment member for engaging the at least one tube engagement member.
56. The solution delivery system according to claim 55, wherein the feeding set adaptor has at least two tube engagement members and wherein the pump engagement portion of the infusion set has a central working portion and at least two abutment members, one being disposed adjacent opposing ends of the central working portion and configured to engage the tube engagement members .
57. The solution delivery system according to claim 56, wherein the system further comprises an enteral feeding pump with a rotor, and wherein at least one tube engagement member and at least one abutment member is disposed on the upstream side rotor and at least one tube engagement member and at least one abutment member is disposed on a downstream side of the rotor. 58. The solution delivery system according to claim 57, further comprising an optical sensor disposed adjacent the at least one tube engagement member disposed upstream from the rotor and configured to detect pressure in a flexible tube forming the pump engagement portion of an infusion set adjacent said at least one tube engagement member.
59. The solution delivery system according to claim 57, further comprising an optical sensor disposed adjacent the at least one tube engagement member disposed downstream from the rotor and configured to detect pressure in the in a flexible tube forming the pump engagement portion of an infusion set adjacent said at least one tube engagement member .
60. The solution delivery system according to - claim 55, wherein the tube engagement member defines a recess, and wherein the abutment member is received in the recess.
61. The solution delivery system according to claim 60, wherein the adaptor has a first tube engagement member and a second tube engagement member and wherein the pump engaging portion has a first abutment member which engages the first tube engagement member and a second abutment member which engages the second tube engagement member, and a space between the first and second abutment members forming a monitoring portion.
62. The solution delivery system according to claim 61, wherein the system further comprises an optical sensor disposed adjacent the monitoring portion and configured to measure expansion and contraction of the monitoring portion.
63. The solution delivery system according to claim 61, wherein the adaptor has a third tube engagement member and a fourth tube engagement member and wherein the pump engaging portion has a third abutment member which engages the third tube engagement member and a fourth abutment member which engages the fourth tube engagement member, and a space between the third and fourth abutment members forming a monitoring portion.
64. The solution delivery system according to claim 63, wherein the system further comprises an optical sensor disposed adjacent the monitoring portion between the third and fourth abutment members and configured to measure expansion and contraction of said monitoring portion. 65. The solution1 delivery system according to claim 64, further comprising a means for generating an alarm when a pressure in a monitoring portion falls outside a predetermined range .
66. A feeding set adaptor for use with an infusion set, the feeding set adaptor having at least two tube engagement members configured for receiving and engaging a pump engaging portion of an infusion set, at least one of the at least two tube engagement members being configured for engaging an upstream portion of the pump engaging portion and at least one of the at least two tube engagement members being configured for engaging a downstream portion of the pump engaging portion.
67. The feeding set adaptor according to claim 66, wherein the tube engagement members comprise flanges for securing the pump engagement portion.
68. The feeding set adaptor according to claim 66, further comprising a first connector configured for attachment to an inflow line of an infusion set and a second connector configured for attachment to an outflow line of an infusion set.
69. The feeding set adaptor according to claim 66 , wherein the feeding set adaptor further comprises an anti-freeflow mechanism. 70. The feeding set adaptor according to claim 69, wherein the anti-freeflow mechanism comprises a stop sized for disposition inside a tube of an infusion set.
71. The feeding set adaptor according to claim 69 , wherein the anti-freeflow adaptor comprises a flap.
72. A solution delivery system including a feeding set adaptor in accordance with claim 66, further comprising a flexible tube forming a pump engaging portion of an infusion set. 73. The solution delivery system according to claim 72, wherein the flexible tube engages the tube engagement members and forms at least one monitoring portion.
74. The solution delivery system according to claim 73, wherein the flexible tube has a first monitoring portion and a second monitoring portion.
75. The solution delivery system according to claim 74, wherein the system further comprises a pumping mechanism and wherein the first monitoring portion is disposed upstream from the pumping mechanism and the second monitoring portions is disposed downstream from the pumping mechanism.
76. The solution delivery system according to claim 74, wherein the feeding adaptor has a first tube engagement member and a second tube engagement member spaced apart from one another, and wherein the first monitoring portion is disposed between the first and second tube engagement members .
77. The solution delivery system according to claim 76, wherein the flexible tube has a first abutment member and a second abutment member for engaging the first tube engagement member and the second tube engagement member, respectively, to thereby limit axial movement of the flexible tube. 78. The solution delivery system according to claim 76, further comprising an optical sensor disposed adjacent the first and second tube engagement members .
79. The solution delivery system according to claim 76, wherein the feeding set adaptor has a third tube engagement member and a fourth tube engagement member and wherein the flexible tube has a third abutment member and a fourth abutment member for engaging the third tube engagement member and the fourth tube engagement member, respectively, to thereby limit axial movement of the flexible tube. 80. The feeding set adaptor according to claim 66, further comprising a sample cell.
81. The feeding set adaptor according to claim 80, wherein the feeding set adaptor has a first connector and a second connector and wherein the sample cell is disposed in one of the first and second connectors .
82. The feeding set adaptor according to claim 80, wherein the sample cell has a pair of sidewalls disposed at an angle of between about 45 and 100 degrees from one another.
83. The feeding set adaptor according to claim 82, wherein the sample cell has a base portion configured for transmitting light regardless of the contents of the sample cell. 84. A solution delivery system according to claim 82, further comprising a housing disposed adjacent the sample cell.
85. The solution delivery system according to claim 84, wherein the housing has a pair of sidewalls disposed at an angle of 50 to 60 degrees from one another .
86. A solution delivery system according to claim 82, further comprising an optical sensor disposed to transmit light into and detect light refracted in the sample cell.
87. A method for forming an infusion set, the method comprising; selecting a feeding set adaptor having a first connector and a second connector formed integrally together; attaching an infusion set inflow line to the first connector; attaching an infusion set outflow line to the second connector; and attaching a pump engaging portion of an infusion set to the first and second connectors so that the inflow line, the pump engaging portion and the outflow line are in fluid communication with one another.
88. The method according to claim 87, wherein the method comprises selecting a feeding set adaptor having an anti-freeflow mechanism. 89. The method according to claim 87, wherein the method comprises selecting a feeding set adaptor having a sample cell formed thereon.
90. The method according to claim 87, wherein the method comprises attaching the pump engaging portion to the feeding set adaptor to form at least one monitoring portion which has limited axial movement .
91. A method for monitoring pressure in an infusion set, the method comprising: selecting a feeding set adaptor having a pump engaging portion of an infusion set disposed thereon and defining a monitoring portion; and disposing the monitoring portion in an optical sensor to detect pressure changes in the monitoring portion by changes in the diameter of the monitoring portion.
92. A method for preventing freeflow in an infusion set, the method comprising: selecting a feeding set adaptor having a pump engaging portion of an infusion set disposed thereon and defining a monitoring portion and an anti-freeflow mechanism configured to selectively stop fluid flow through the infusion set; and disposing the anti-freeflow mechanism in the infusion set to selectively preclude fluid flow therethrough.
93. A method for detecting air bubbles passing through an infusion set, the method comprising; selecting a feeding set adaptor having a sample cell formed thereon and having a pump engaging portion attached thereto; passing solution through the sample cell; and disposing the sample cell in an optical signal such that light is refracted differently when air is present in the sample cell than when solution is present in the sample cell to thereby determine the presence of air.
94. The method according to claim 93, wherein the method comprises emitting the light in a plane and positioning the sample cell so that a sidewall of the sample cell is at an angle less than normal to the plane.
PCT/US2001/047884 2001-04-16 2001-12-11 Feeding set adaptor WO2002083204A1 (en)

Priority Applications (4)

Application Number Priority Date Filing Date Title
EP01991001.7A EP1381412B1 (en) 2001-04-16 2001-12-11 Feeding set adaptor
DK01991001.7T DK1381412T3 (en) 2001-04-16 2001-12-11 NUTRITION ADAPT ADAPTER
JP2002581005A JP4255695B2 (en) 2001-04-16 2001-12-11 Adapter for feeding device
ES01991001.7T ES2496101T3 (en) 2001-04-16 2001-12-11 Power set adapter

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
US09/836,851 US6659976B2 (en) 2001-04-16 2001-04-16 Feeding set adaptor
US09/836,851 2001-04-16

Publications (1)

Publication Number Publication Date
WO2002083204A1 true WO2002083204A1 (en) 2002-10-24

Family

ID=25272887

Family Applications (1)

Application Number Title Priority Date Filing Date
PCT/US2001/047884 WO2002083204A1 (en) 2001-04-16 2001-12-11 Feeding set adaptor

Country Status (7)

Country Link
US (3) US6659976B2 (en)
EP (2) EP2596819B1 (en)
JP (2) JP4255695B2 (en)
CN (1) CN1275658C (en)
DK (2) DK1381412T3 (en)
ES (2) ES2496101T3 (en)
WO (1) WO2002083204A1 (en)

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7722573B2 (en) 2006-03-02 2010-05-25 Covidien Ag Pumping apparatus with secure loading features
US7758551B2 (en) 2006-03-02 2010-07-20 Covidien Ag Pump set with secure loading features
US7763005B2 (en) 2006-03-02 2010-07-27 Covidien Ag Method for using a pump set having secure loading features
US7927304B2 (en) 2006-03-02 2011-04-19 Tyco Healthcare Group Lp Enteral feeding pump and feeding set therefor
US11889817B2 (en) 2013-08-13 2024-02-06 Tg Medwise Ltd. Substance delivery device

Families Citing this family (136)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7815612B2 (en) * 2000-05-11 2010-10-19 Zevex, Inc. Apparatus and method for preventing free flow in an infusion line
US7150727B2 (en) * 2000-05-11 2006-12-19 Zevex, Inc. Apparatus and method for preventing free flow in an infusion line
US6595950B1 (en) * 2000-05-11 2003-07-22 Zevex, Inc. Apparatus and method for preventing free flow in an infusion line
US6531708B1 (en) 2001-04-16 2003-03-11 Zevex, Inc. Optical bubble detection system
US6659976B2 (en) * 2001-04-16 2003-12-09 Zevek, Inc. Feeding set adaptor
US6523414B1 (en) * 2001-04-16 2003-02-25 Zevex, Inc. Optical pressure monitoring system
US7578825B2 (en) * 2004-04-19 2009-08-25 Acumed Llc Placement of fasteners into bone
US7527608B2 (en) * 2002-08-12 2009-05-05 Lma North America, Inc. Medication infusion and aspiration system and method
US7794423B2 (en) * 2004-05-25 2010-09-14 Covidien Ag Re-certification system for a flow control apparatus
US7092797B2 (en) * 2004-05-25 2006-08-15 Sherwood Services Ag Flow monitoring system for a flow control apparatus
US7462170B2 (en) * 2004-05-25 2008-12-09 Covidien Ag Administration feeding set and valve mechanism
DK1618916T3 (en) * 2004-07-22 2008-08-04 Woo Young Medical Co Ltd Automatic shut-off valve for injecting drugs
CN100428965C (en) * 2004-08-05 2008-10-29 株式会社玗荣医疗器 Liquid medicine injection device
US7846131B2 (en) * 2005-09-30 2010-12-07 Covidien Ag Administration feeding set and flow control apparatus with secure loading features
US7534099B2 (en) * 2005-09-30 2009-05-19 Covidien Ag Aliquot correction for feeding set degradation
US20070088269A1 (en) * 2005-09-30 2007-04-19 Sherwood Services Ag Medical pump with lockout system
US7896859B2 (en) 2005-10-20 2011-03-01 Tyco Healthcare Group Lp Enteral feeding set
US8011905B2 (en) * 2005-11-17 2011-09-06 Novartis Ag Surgical cassette
US7722562B2 (en) 2006-03-02 2010-05-25 Tyco Healthcare Group Lp Pump set with safety interlock
US8021336B2 (en) 2007-01-05 2011-09-20 Tyco Healthcare Group Lp Pump set for administering fluid with secure loading features and manufacture of component therefor
US7805978B2 (en) 2006-10-24 2010-10-05 Zevex, Inc. Method for making and using an air bubble detector
US10959881B2 (en) 2006-11-09 2021-03-30 Johnson & Johnson Surgical Vision, Inc. Fluidics cassette for ocular surgical system
US8414534B2 (en) 2006-11-09 2013-04-09 Abbott Medical Optics Inc. Holding tank devices, systems, and methods for surgical fluidics cassette
US8491528B2 (en) 2006-11-09 2013-07-23 Abbott Medical Optics Inc. Critical alignment of fluidics cassettes
US7560686B2 (en) * 2006-12-11 2009-07-14 Tyco Healthcare Group Lp Pump set and pump with electromagnetic radiation operated interlock
US10342701B2 (en) 2007-08-13 2019-07-09 Johnson & Johnson Surgical Vision, Inc. Systems and methods for phacoemulsification with vacuum based pumps
US7981082B2 (en) * 2007-08-21 2011-07-19 Hospira, Inc. System and method for reducing air bubbles in a fluid delivery line
US7987722B2 (en) 2007-08-24 2011-08-02 Zevex, Inc. Ultrasonic air and fluid detector
DE102007049446A1 (en) 2007-10-16 2009-04-23 Cequr Aps Catheter introducer
US9026370B2 (en) 2007-12-18 2015-05-05 Hospira, Inc. User interface improvements for medical devices
CA2712945C (en) 2008-01-23 2017-06-06 Deka Products Limited Partnership Pump cassette and methods for use in medical treatment system using a plurality of fluid lines
US8425470B2 (en) * 2008-04-01 2013-04-23 Zevex, Inc. Anti-free-flow mechanism for enteral feeding pumps
WO2009124091A1 (en) * 2008-04-01 2009-10-08 Zevex, Inc. Anti-free flow mechanism for enteral feeding pumps
USD636077S1 (en) 2008-08-27 2011-04-12 Deka Products Limited Partnership Fluidic connector
US9005157B2 (en) 2008-11-07 2015-04-14 Abbott Medical Optics Inc. Surgical cassette apparatus
CA2743086C (en) 2008-11-07 2017-12-05 Abbott Medical Optics Inc. Automatically pulsing different aspiration levels to an ocular probe
CA2743098C (en) 2008-11-07 2017-08-15 Abbott Medical Optics Inc. Automatically switching different aspiration levels and/or pumps to an ocular probe
WO2010091314A2 (en) 2009-02-06 2010-08-12 Zevex, Inc. Air bubble detector
WO2010091313A2 (en) 2009-02-06 2010-08-12 Zevex, Inc. Automatic safety occluder
EP2405968B1 (en) * 2009-03-06 2015-01-14 DEKA Products Limited Partnership Devices and methods for occluding a flexible tube
US9492317B2 (en) 2009-03-31 2016-11-15 Abbott Medical Optics Inc. Cassette capture mechanism
US20100282766A1 (en) * 2009-05-06 2010-11-11 Heiko Arndt Low-Dead Volume Microfluidic Component and Method
US8230744B2 (en) 2009-05-06 2012-07-31 Cequr Sa Low-dead volume microfluidic circuit and methods
AU2009348770B2 (en) * 2009-06-25 2015-04-02 Nestec S.A. Pinch clamp assembly for an infusion cassette
WO2011008621A1 (en) 2009-07-13 2011-01-20 Nestec S.A. Infra-red reflective air-in-line sensor systems
US8986252B2 (en) * 2009-07-13 2015-03-24 Nestec S.A. Cassettes and methods of using same
EP2453949B1 (en) * 2009-07-13 2017-02-08 Nestec S.A. Cassette with infusion set containing anti-freeflow ball valve for peristaltic infusion pump
US8547239B2 (en) * 2009-08-18 2013-10-01 Cequr Sa Methods for detecting failure states in a medicine delivery device
US8672873B2 (en) 2009-08-18 2014-03-18 Cequr Sa Medicine delivery device having detachable pressure sensing unit
MX2012002401A (en) 2009-08-26 2012-04-02 Nestec Sa Infra-red reflective occlusion sensors.
IN2012DN01688A (en) 2009-08-31 2015-05-22 Nestec Sa
US9364651B2 (en) 2010-02-23 2016-06-14 Smiths Medical Asd, Inc. Adapter with special fitting
US8876798B2 (en) * 2010-02-23 2014-11-04 Smiths Medical Asd, Inc. Catheter adapter
US8154274B2 (en) 2010-05-11 2012-04-10 Tyco Healthcare Group Lp Safety interlock
EP3279703B2 (en) * 2010-07-07 2022-06-29 DEKA Products Limited Partnership Medical treatment system and methods using a plurality of fluid lines
DE102010033241A1 (en) * 2010-08-03 2012-02-09 Fresenius Medical Care Deutschland Gmbh Device with a hose roller pump and method for this purpose
US8486020B2 (en) * 2010-08-11 2013-07-16 Zevex, Inc. Pressure sensor and method of use
US8377000B2 (en) * 2010-10-01 2013-02-19 Abbott Laboratories Enteral feeding apparatus having a feeding set
USD672455S1 (en) 2010-10-01 2012-12-11 Zevex, Inc. Fluid delivery cassette
CA2812764C (en) 2010-10-01 2016-04-26 Zevex, Inc. Anti free-flow occluder and priming actuator pad
AU2011308757B2 (en) 2010-10-01 2015-03-12 Zevex, Inc. Pressure monitoring system for infusion pumps
EP2621556B1 (en) 2010-10-01 2020-06-10 Zevex, Inc. Method for improving accuracy in a peristaltic pump system based on tubing material properties
CN103260671B (en) * 2010-10-01 2015-10-21 泽维克斯公司 Pressure sensor seals and using method
US8377001B2 (en) * 2010-10-01 2013-02-19 Abbott Laboratories Feeding set for a peristaltic pump system
US9211378B2 (en) 2010-10-22 2015-12-15 Cequr Sa Methods and systems for dosing a medicament
EP2718680B1 (en) 2011-06-07 2023-12-27 Measurement Specialties, Inc. Optical sensing device for fluid sensing and method therefor
US9033923B2 (en) 2011-07-25 2015-05-19 Nestec S.A. Infrared reflective air-in-line sensor system
EP2745204A4 (en) 2011-08-19 2015-01-07 Hospira Inc Systems and methods for a graphical interface including a graphical representation of medical data
EP2749858B1 (en) * 2011-08-22 2018-04-25 Nikkiso Company Limited Fluid flow path pressure detection device
GB2495937A (en) 2011-10-25 2013-05-01 Watson Marlow Ltd Peristaltic pump head with auxiliary leakage chamber
GB2495935A (en) 2011-10-25 2013-05-01 Watson Marlow Ltd Peristaltic pump with tube end fitting
GB2495936B (en) 2011-10-25 2018-05-23 Watson Marlow Ltd Peristaltic pump and pumphead therefor
WO2013090709A1 (en) 2011-12-16 2013-06-20 Hospira, Inc. System for monitoring and delivering medication to a patient and method of using the same to minimize the risks associated with automated therapy
US8733178B2 (en) * 2012-02-01 2014-05-27 Baxter Healthcare S.A. Pressure sensing assembly and method for an infusion pump
US9101712B2 (en) * 2012-03-09 2015-08-11 Zevex, Inc. Occlusion detection method
EP2825219B1 (en) * 2012-03-17 2023-05-24 Johnson & Johnson Surgical Vision, Inc. Surgical cassette
EP2830687B1 (en) 2012-03-30 2019-07-24 ICU Medical, Inc. Air detection system and method for detecting air in a pump of an infusion system
US10737087B2 (en) 2012-04-17 2020-08-11 Smiths Medical Asd, Inc. Filling fitting
US9016137B2 (en) * 2012-05-15 2015-04-28 Sonotec Ultraschallsenosorik Halle Gmbh Device for the contactless flow measurement of fluids in flexible tubes
DE102012105918A1 (en) * 2012-07-03 2014-01-09 B. Braun Avitum Ag Multi-connector and medical device for extracorporeal blood treatment with multi-connector detection
US9710610B2 (en) 2012-07-25 2017-07-18 Covidien Lp Enteral feeding pump with flow adjustment
EP3586891A1 (en) 2012-07-31 2020-01-01 ICU Medical, Inc. Patient care system for critical medications
EP3607980A1 (en) * 2012-08-13 2020-02-12 TG Medwise Ltd. Substance delivery device
WO2014062403A1 (en) 2012-10-15 2014-04-24 Smiths Medical Asd, Inc. Infusion system disposable alignment system
JP5587958B2 (en) 2012-10-19 2014-09-10 日機装株式会社 Ironing type pump
JP5469728B1 (en) 2012-10-19 2014-04-16 日機装株式会社 Liquid channel pressure detector
CN103100124B (en) * 2013-01-25 2015-05-20 东莞市众隆电机电器制造有限公司 Medical fluid pump device
CA2913421C (en) 2013-05-24 2022-02-15 Hospira, Inc. Multi-sensor infusion system for detecting air or an occlusion in the infusion system
EP3003442B1 (en) 2013-05-29 2020-12-30 ICU Medical, Inc. Infusion system and method of use which prevents over-saturation of an analog-to-digital converter
CA2913915C (en) 2013-05-29 2022-03-29 Hospira, Inc. Infusion system which utilizes one or more sensors and additional information to make an air determination regarding the infusion system
CN104436365B (en) * 2013-07-03 2017-09-29 李耀强 A kind of isolator
ES2881386T3 (en) 2013-09-24 2021-11-29 Kpr Us Llc Feeding set and enteral feeding pump
USD735320S1 (en) * 2013-11-30 2015-07-28 Zevex, Inc. Enteral feeding pump cassette
USD739931S1 (en) * 2013-11-30 2015-09-29 Zevex, Inc. Enteral feeding pump cassette
US10080836B2 (en) 2014-01-23 2018-09-25 Zevex, Inc. Absorption-based optical sensor for detecting infusion pump cassette
ES2776363T3 (en) 2014-02-28 2020-07-30 Icu Medical Inc Infusion set and method using dual wavelength in-line optical air detection
JP5863871B2 (en) 2014-04-15 2016-02-17 日機装株式会社 Mounting member and ironing pump
USD743023S1 (en) 2014-04-15 2015-11-10 Zevex, Inc. Enteral feeding pump interface
WO2015184366A1 (en) 2014-05-29 2015-12-03 Hospira, Inc. Infusion system and pump with configurable closed loop delivery rate catch-up
EP4321144A3 (en) * 2014-07-25 2024-04-10 Kpr U.S., Llc Detection system for flow control apparatus
JP6628796B2 (en) 2014-10-15 2020-01-15 ケイピーアール ユーエス エルエルシー Flow control device and method of operating the same
US9642965B2 (en) 2014-12-12 2017-05-09 Zevex, Inc. Infusion pump cassette and cassette interface configured to assist cassette removal
KR101646897B1 (en) * 2014-12-17 2016-08-12 제벡스, 아이엔씨. Infusion pump cassette having finger-bypassed in-line occluder
US11344668B2 (en) 2014-12-19 2022-05-31 Icu Medical, Inc. Infusion system with concurrent TPN/insulin infusion
US10850024B2 (en) 2015-03-02 2020-12-01 Icu Medical, Inc. Infusion system, device, and method having advanced infusion features
CN107683151B (en) 2015-06-24 2020-07-28 日机装株式会社 Blood purification device
US20170120039A1 (en) * 2015-11-04 2017-05-04 Depuy Mitek, Llc Anti-Clogging Fluid Management System
EP3405249B1 (en) * 2015-12-24 2023-06-21 Heriot Eyecare Pty. Ltd. Pressure management device
AU2017264784B2 (en) 2016-05-13 2022-04-21 Icu Medical, Inc. Infusion pump system and method with common line auto flush
AU2017269150B2 (en) * 2016-05-25 2020-03-05 Zevex, Inc. Sensing system for multiple lumen tubing
WO2017214441A1 (en) 2016-06-10 2017-12-14 Icu Medical, Inc. Acoustic flow sensor for continuous medication flow measurements and feedback control of infusion
JP6882346B2 (en) 2016-06-16 2021-06-02 スミスズ メディカル エーエスディー,インコーポレイティド Assembly and method for infusion pump system dosing set
DE102017102829A1 (en) * 2017-02-13 2018-08-16 Cardiobridge Gmbh flushing system
JP7004991B2 (en) 2017-02-14 2022-01-21 サーパス工業株式会社 Tube pump and holding mechanism
CN110944697B (en) 2017-07-19 2022-09-09 史密斯医疗Asd公司 Casing arrangement for infusion pump
USD870263S1 (en) 2017-07-26 2019-12-17 Smiths Medical Asd, Inc. Infusion set
JP6464238B1 (en) 2017-09-07 2019-02-06 日機装株式会社 Blood purification apparatus and method for discharging bubbles
JP6462077B1 (en) 2017-09-07 2019-01-30 日機装株式会社 Blood purification apparatus and method for discharging bubbles
EP3703780B1 (en) * 2017-10-31 2022-07-06 CME America, LLC Cartridge for tubing placement in a peristaltic infusion pump
US10089055B1 (en) 2017-12-27 2018-10-02 Icu Medical, Inc. Synchronized display of screen content on networked devices
CN108175906B (en) * 2017-12-28 2019-02-26 北京灵泽医药技术开发有限公司 Fluid control devices
CN107982600B (en) * 2017-12-28 2018-10-23 北京灵泽医药技术开发有限公司 Detection device and corresponding fluid control devices
USD882759S1 (en) 2018-05-14 2020-04-28 Zevex, Inc. In-line occluder
JP7178838B2 (en) * 2018-09-11 2022-11-28 大研医器株式会社 Connection member, pump casing and injection device provided with said connection member
US11213460B2 (en) 2018-09-19 2022-01-04 Vesco Medical Llc Connectors for infusion pump feeding sets
US20200254985A1 (en) * 2019-02-12 2020-08-13 The Goodyear Tire & Rubber Company Brake pressure sensor for determination of braking efficiency
EP3705148A1 (en) 2019-03-04 2020-09-09 Avoset Health Ltd. In cycle pressure measurement
WO2020178827A1 (en) 2019-03-05 2020-09-10 Avoset Health Ltd. Anti-free-flow valve
US11278671B2 (en) 2019-12-04 2022-03-22 Icu Medical, Inc. Infusion pump with safety sequence keypad
CN111407966A (en) * 2020-04-02 2020-07-14 长沙巨翊医疗科技有限公司 Infusion pump pipeline clamping cover device
WO2022020184A1 (en) 2020-07-21 2022-01-27 Icu Medical, Inc. Fluid transfer devices and methods of use
US11135360B1 (en) 2020-12-07 2021-10-05 Icu Medical, Inc. Concurrent infusion with common line auto flush
USD999369S1 (en) 2021-06-09 2023-09-19 Zevex, Inc. In-line occluder
CN113499507B (en) * 2021-07-14 2022-09-23 巨翊科技(上海)有限公司 Automatic clamp and mechanism for infusion tube
DE102021126851A1 (en) * 2021-10-15 2023-04-20 Elixion Medical GmbH Device and method for flow determination
CN115337493A (en) * 2021-10-22 2022-11-15 武汉迈瑞医疗技术研究院有限公司 Medical pump and pipeline assembly thereof

Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5704584A (en) * 1995-03-27 1998-01-06 Zevex, Inc. Pinch clip occluder for infusion sets
US5720271A (en) * 1995-04-22 1998-02-24 Hauser; Charles Process for the orientation of single crystals for cutting in a cutting machine and device for practicing this process
US5853386A (en) * 1996-07-25 1998-12-29 Alaris Medical Systems, Inc. Infusion device with disposable elements

Family Cites Families (96)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US534708A (en) * 1895-02-26 Faucet-bung
US455949A (en) * 1891-07-14 Albert a
US463129A (en) * 1891-11-10 And sidney
US410675A (en) * 1889-09-10 Heel-nail
US2471623A (en) 1944-12-19 1949-05-31 Adrian O Hubbell Apparatus for handling fluids
FR968833A (en) * 1947-07-09 1950-12-06 Ponctiovid Societe A Responsab Sterile equipment for blood sampling or aseptic injection
US2858095A (en) 1955-08-26 1958-10-28 Gen Motors Corp Valving device
US2999499A (en) * 1958-07-11 1961-09-12 Cutter Lab Flexible check valve
US3090222A (en) 1960-02-17 1963-05-21 Kurashiki Rayon Co Apparatus for continuous measurement of degree of polymerization
US3209596A (en) * 1962-07-18 1965-10-05 Thomas E Kelly Pressure sensing instrument
US3329391A (en) 1964-09-28 1967-07-04 William V Deane Surgical pinch valve
US3213882A (en) 1965-02-08 1965-10-26 David L Beatty Pneumatic control valve
US3450476A (en) 1966-02-03 1969-06-17 Hewlett Packard Co Apparatus for measuring the index of refraction of a fluid medium
US3998364A (en) 1974-04-15 1976-12-21 Bruce Lee Hollander Dispensing valve for bottled carbonated beverages
US4065093A (en) * 1976-05-24 1977-12-27 Baxter Travenol Laboratories, Inc. Flow control device
US4106675A (en) * 1976-12-22 1978-08-15 The Kendall Company Liquid sampling device
US4142645A (en) * 1978-04-12 1979-03-06 Walton Donald G Vacuum sealing closure lid for home canning operations
US4193004A (en) 1978-06-22 1980-03-11 Cobe Laboratories, Inc. Fluid level monitoring through fluid cell protrusion
US4230151A (en) 1979-01-24 1980-10-28 Jonsson Ulf R S Pinch valve
US4236880A (en) 1979-03-09 1980-12-02 Archibald Development Labs, Inc. Nonpulsating IV pump and disposable pump chamber
US4244365A (en) 1979-03-26 1981-01-13 Cutter Laboratories, Inc. Device for use in detecting occlusion in an infusion system
US4381591A (en) * 1979-04-24 1983-05-03 American Hospital Supply Corporation Method of assembling medical flushing valve
US4382453A (en) 1979-06-27 1983-05-10 Abbott Laboratories Flow ristrictor for flexible tubing
DE2937484A1 (en) 1979-09-17 1981-05-14 Siemens AG, 1000 Berlin und 8000 München OPTICAL DEVICE FOR MEASURING PRESSURE DIFFERENCES BY LIGHT INTENSITY CHANGE
DE2937511A1 (en) 1979-09-17 1981-05-07 Siemens AG, 1000 Berlin und 8000 München OPTICAL DEVICE FOR MEASURING LOW PRESSURE DIFFERENCES BY MEANS OF LIGHT INTENSITY CHANGE
US4312341A (en) 1979-12-13 1982-01-26 Baxter Travenol Laboratories, Inc. Bubble detector
US4425116A (en) 1980-04-14 1984-01-10 Baxter Travenol Laboratories, Inc. Control system for fluid flow apparatus
US4453295A (en) 1981-06-17 1984-06-12 Solco Basel Ag Device for pinching-off hoses
US4645489A (en) 1982-11-30 1987-02-24 Beta Phase, Inc. Fluid delivery apparatus with shape-memory flow control element
US4559454A (en) 1983-04-01 1985-12-17 Kramer Donald L Bubble detecting infusion apparatus
US4559045A (en) 1983-05-10 1985-12-17 Anatros Corporation Pinch valve assembly
US4624663A (en) 1983-05-10 1986-11-25 Critikon, Inc. Pinch valve assembly
US4527588A (en) * 1983-12-14 1985-07-09 Warner-Lambert Company Safety valve
EP0150666B1 (en) 1983-12-27 1988-10-12 Alfred Pfister-Lehmann Closure at a ureteral catheter
DE3405026A1 (en) 1984-02-13 1985-08-14 Philips Patentverwaltung Gmbh, 2000 Hamburg OPTICAL PRESSURE SENSOR
US4555949A (en) 1984-05-04 1985-12-03 Anatros Corporation Optical fluid pressure sensor
US4554837A (en) 1984-05-04 1985-11-26 Anatros Corporation Reflective optical fluid pressure sensor
GB8424101D0 (en) 1984-09-24 1984-10-31 Vi Tal Hospital Products Ltd Air-in-line detector
US4634092A (en) 1984-09-30 1987-01-06 Fisher & Paykel, Private Bag Clamp valves
US4524802A (en) 1984-10-01 1985-06-25 Bio-Chem Valve Corp. Pinch valve
US4631529A (en) 1984-10-17 1986-12-23 Ivek Corporation Electro-optical fluid detector
JPS61197532A (en) * 1985-02-27 1986-09-01 Isao Mochida Production of vinylidene chloride
US4689043A (en) 1986-03-19 1987-08-25 Imed Corporation IV tube activator
US4762518A (en) 1986-08-01 1988-08-09 Pancretec, Inc. Blockage hazard alarm in an intravenous system
DE3783112D1 (en) 1986-09-24 1993-01-28 Cannonbear Inc SENSOR AND METHOD FOR DETECTING THE LEAKAGE LEVEL AND FLOW.
US4833918A (en) 1986-09-24 1989-05-30 Cannonbear, Inc. Sensor and method for ullage level and flow detection
US4728324A (en) 1986-10-15 1988-03-01 The Kendall Company Urine meter valve with tamper indicator
US4762515A (en) * 1987-01-06 1988-08-09 Ivy Laboratories, Inc. Medicament implant applicator
US4730635A (en) * 1987-08-19 1988-03-15 Hall Surgical Valve and method
DE3731242A1 (en) 1987-09-17 1989-03-30 Joka Kathetertechnik Gmbh SHUT-OFF DEVICE ON A LIQUID DRAWING OR INFUSION DEVICE
US4908676A (en) 1987-12-18 1990-03-13 Bio-Recovery Systems, Inc. Sensors for dissolved substances in fluids
WO1989003978A1 (en) 1988-03-22 1989-05-05 Conax Buffalo Corporation Optical liquid level sensor
JPH01249064A (en) 1988-03-30 1989-10-04 Nikkiso Co Ltd Detection of closed state of infusion pipe and device therefor
US5015091A (en) 1988-04-13 1991-05-14 Mitsubishi Denki K.K. Device for detecting alcoholic content
US4884065A (en) 1988-06-13 1989-11-28 Pacesetter Infusion, Ltd. Monitor for detecting tube position and air bubbles in tube
US4881487A (en) 1988-11-21 1989-11-21 Micron Technology Inc. Fluid level sensing method and apparatus
US4920336A (en) 1988-11-22 1990-04-24 Fisher Scientific Company Method and apparatus for monitoring the level of the contents in a container
US4913401A (en) * 1989-01-26 1990-04-03 Respironics, Inc. Valve apparatus
US5017192A (en) 1989-10-20 1991-05-21 Minnesota Mining And Manufacturing Company Free flow prevention system for infusion pump
US5020562A (en) * 1989-11-28 1991-06-04 Imed Corporation Multiline check valve assembly
US5083561B1 (en) 1990-06-14 1993-05-18 D. Russo Ronald Tracheal suction catheter
US5116759A (en) 1990-06-27 1992-05-26 Fiberchem Inc. Reservoir chemical sensors
US5022422A (en) * 1990-07-30 1991-06-11 Imed Corporation Ball valve
JPH0693916B2 (en) 1990-10-31 1994-11-24 テルモ株式会社 Infusion pump
US5260665A (en) 1991-04-30 1993-11-09 Ivac Corporation In-line fluid monitor system and method
US5305237A (en) 1991-07-12 1994-04-19 Union Tank Car Company Method and apparatus for monitoring a flowable material in a transportable vessel
DK48092D0 (en) 1992-04-10 1992-04-10 Novo Nordisk As APPARATUS
US5257978A (en) 1992-07-14 1993-11-02 Habley Medical Technology Corporation IV safety module
US5238218A (en) 1992-07-15 1993-08-24 Mackal Glenn H Tube clamp
US5422495A (en) 1993-04-15 1995-06-06 Boston Advanced Technologies, Inc. Optical sensor having a floatation means for detecting fluids through refractive index measurement
US5265847A (en) * 1993-05-03 1993-11-30 Vorhis Daniel J Squeeze valve with augmented sealing
US5534708A (en) 1993-12-15 1996-07-09 Simmonds Precision Products Inc. Optical fuel/air/water sensor and detector circuit
US5396925A (en) * 1993-12-16 1995-03-14 Abbott Laboratories Anti-free flow valve, enabling fluid flow as a function of pressure and selectively opened to enable free flow
US5680111A (en) 1994-02-05 1997-10-21 Baxter International Inc. Dual sensor air-in-line detector
US5482446A (en) * 1994-03-09 1996-01-09 Baxter International Inc. Ambulatory infusion pump
JP3263533B2 (en) 1994-05-17 2002-03-04 ブラザー工業株式会社 Toner remaining amount detecting device and toner storing device thereof
US5695473A (en) 1994-07-27 1997-12-09 Sims Deltec, Inc. Occlusion detection system for an infusion pump
US5568912A (en) * 1994-09-12 1996-10-29 Ivac Corporation Sliding flow controller having channel with variable size groove
US6142979A (en) * 1995-03-27 2000-11-07 Zevex Pinch clip occluder system for infusion sets
US5514102A (en) 1995-05-05 1996-05-07 Zevex Incorporated Pressure monitoring enteral feeding system and method
AU7066996A (en) 1995-11-15 1997-05-22 Arkray, Inc. Liquid detection method and device therefor
US5672887A (en) 1995-11-29 1997-09-30 Shaw; Benjamin G. Optical detector for air in fluid line the same
GB2338758B (en) * 1996-04-10 2000-05-17 Baxter Int Volumetric infusion pump
DE19616952C1 (en) 1996-04-27 1997-01-23 Karlsruhe Forschzent Tactile optoelectronic pressure sensor
US5826621A (en) 1996-08-05 1998-10-27 Alaris Medical Systems, Inc. Valve apparatus
US5807312A (en) * 1997-05-23 1998-09-15 Dzwonkiewicz; Mark R. Bolus pump apparatus
US5983825A (en) * 1998-02-20 1999-11-16 Nowak Products, Inc. Flag protective device
US6396583B1 (en) * 2000-01-31 2002-05-28 Ethicon, Inc. Optical fluid sensor
US7815612B2 (en) 2000-05-11 2010-10-19 Zevex, Inc. Apparatus and method for preventing free flow in an infusion line
US7150727B2 (en) 2000-05-11 2006-12-19 Zevex, Inc. Apparatus and method for preventing free flow in an infusion line
US6595950B1 (en) 2000-05-11 2003-07-22 Zevex, Inc. Apparatus and method for preventing free flow in an infusion line
US6494864B1 (en) * 2000-08-29 2002-12-17 Sherwood Services, Ag Inner lumen anti-free flow device
US6412160B1 (en) * 2000-09-22 2002-07-02 General Electric Company Swaged tube fitting collar and die
US6531708B1 (en) 2001-04-16 2003-03-11 Zevex, Inc. Optical bubble detection system
US6659976B2 (en) 2001-04-16 2003-12-09 Zevek, Inc. Feeding set adaptor
US6523414B1 (en) 2001-04-16 2003-02-25 Zevex, Inc. Optical pressure monitoring system

Patent Citations (3)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US5704584A (en) * 1995-03-27 1998-01-06 Zevex, Inc. Pinch clip occluder for infusion sets
US5720271A (en) * 1995-04-22 1998-02-24 Hauser; Charles Process for the orientation of single crystals for cutting in a cutting machine and device for practicing this process
US5853386A (en) * 1996-07-25 1998-12-29 Alaris Medical Systems, Inc. Infusion device with disposable elements

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP1381412A4 *

Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US7722573B2 (en) 2006-03-02 2010-05-25 Covidien Ag Pumping apparatus with secure loading features
US7758551B2 (en) 2006-03-02 2010-07-20 Covidien Ag Pump set with secure loading features
US7763005B2 (en) 2006-03-02 2010-07-27 Covidien Ag Method for using a pump set having secure loading features
US7927304B2 (en) 2006-03-02 2011-04-19 Tyco Healthcare Group Lp Enteral feeding pump and feeding set therefor
US11889817B2 (en) 2013-08-13 2024-02-06 Tg Medwise Ltd. Substance delivery device

Also Published As

Publication number Publication date
US6659976B2 (en) 2003-12-09
JP4870134B2 (en) 2012-02-08
ES2561716T3 (en) 2016-02-29
US20020151838A1 (en) 2002-10-17
EP1381412B1 (en) 2014-06-18
EP1381412A1 (en) 2004-01-21
ES2496101T3 (en) 2014-09-18
JP4255695B2 (en) 2009-04-15
DK2596819T3 (en) 2016-02-15
JP2004528091A (en) 2004-09-16
EP2596819B1 (en) 2015-11-04
DK1381412T3 (en) 2014-09-15
US20040097885A1 (en) 2004-05-20
JP2009022808A (en) 2009-02-05
US7070575B2 (en) 2006-07-04
CN1505533A (en) 2004-06-16
EP1381412A4 (en) 2008-09-10
EP2596819A1 (en) 2013-05-29
US20050209552A1 (en) 2005-09-22
US6852094B2 (en) 2005-02-08
CN1275658C (en) 2006-09-20

Similar Documents

Publication Publication Date Title
EP1381412B1 (en) Feeding set adaptor
US7921718B2 (en) Optical pressure monitoring system
US5514102A (en) Pressure monitoring enteral feeding system and method
ES2418630T3 (en) Empty container detection using a container side pressure sensor
EP0923394B1 (en) Pump system with error detection for clinical nutrition
US4710166A (en) Automated drug additive infusion system
US11278680B2 (en) Measuring valve health by pressure monitoring
EP3735999A2 (en) Enteral feeding pump and tubing set
CA2256392C (en) Pump system with error detection for clinical nutrition

Legal Events

Date Code Title Description
AK Designated states

Kind code of ref document: A1

Designated state(s): AE AG AL AM AT AU AZ BA BB BG BR BY BZ CA CH CN CO CR CU CZ DE DK DM DZ EE ES FI GB GD GE GH GM HR HU ID IL IN IS JP KE KG KP KR KZ LC LK LR LS LT LU LV MA MD MG MK MN MW MX MZ NO NZ PL PT RO RU SD SE SG SI SK SL TJ TM TR TT TZ UA UG UZ VN YU ZA ZW

AL Designated countries for regional patents

Kind code of ref document: A1

Designated state(s): GH GM KE LS MW MZ SD SL SZ TZ UG ZM ZW AM AZ BY KG KZ MD RU TJ TM AT BE CH CY DE DK ES FI FR GB GR IE IT LU MC NL PT SE TR BF BJ CF CG CI CM GA GN GQ GW ML MR NE SN TD TG

121 Ep: the epo has been informed by wipo that ep was designated in this application
DFPE Request for preliminary examination filed prior to expiration of 19th month from priority date (pct application filed before 20040101)
WWE Wipo information: entry into national phase

Ref document number: 2001991001

Country of ref document: EP

WWE Wipo information: entry into national phase

Ref document number: 018231446

Country of ref document: CN

WWE Wipo information: entry into national phase

Ref document number: 2002581005

Country of ref document: JP

WWP Wipo information: published in national office

Ref document number: 2001991001

Country of ref document: EP

REG Reference to national code

Ref country code: DE

Ref legal event code: 8642